Method for inserting and positioning an artificial disc

ABSTRACT

A method for inserting an intervertebral artificial disc is provided with the intervertebral disc including a first endplate having a plurality of protrusions for attaching to an adjacent vertebrae and an extension portion extending towards a second adjacent vertebrae. A second endplate is provided with a plurality of protrusions for attaching to a second adjacent vertebrae and an extension portion extending towards the first adjacent vertebrae. A flexible member having an upper portion and a lower portion and a slider plate positioned within the upper portion of the flexible member is also provided. The extension portion of the first endplate is adapted to fit within a first cavity in the upper portion of the flexible member and the extension portion of the second endplate is adapted to fit within a second cavity in the lower portion of the flexible member.

CROSS-REFERENCE TO RELATED APPLICATIONS

This present application is a continuation of U.S. patent applicationSer. No. 12/466,772 filed on May 15, 2009, which is incorporated in itsentirety herein.

FIELD OF THE INVENTION

The present invention relates to a prosthetic spinal disc for fully orpartially replacing a damaged disc between two vertebrae of a spine. Thepresent invention also relates to a method for implanting a prostheticspinal disc via posterior or posterior lateral implantation, althoughother implantation approaches may also be used.

BACKGROUND OF THE INVENTION

The vertebrate spine is the axis of the skeleton on which a substantialportion of the weight of the body is supported. In humans, the normalspine has seven cervical, twelve thoracic and five lumbar segments. Thelumbar spine sits upon the sacrum, which then attaches to the pelvis,and in turn is supported by the hip and leg bones. The bony vertebralbodies of the spine are separated by intervertebral discs, which act asjoints but allow known degrees of flexion, extension, lateral bending,and axial rotation.

The typical vertebra has a thick anterior bone mass called the vertebralbody, with a neural (vertebral) arch that arises from the posteriorsurface of the vertebral body. The center of adjacent vertebrae aresupported by intervertebral discs. Each neural arch combines with theposterior surface of the vertebral body and encloses a vertebralforamen. The vertebral foramina of adjacent vertebrae are aligned toform a vertebral canal, through which the spinal sac, cord and nerverootlets pass. The portion of the neural arch which extends posteriorlyand acts to protect the spinal cord's posterior side is known as thelamina. Projecting from the posterior region of the neural arch is thespinous process.

The intervertebral disc primarily serves as a mechanical cushionpermitting controlled motion between vertebral segments of the axialskeleton. The normal disc is a unique, mixed structure, comprised ofthree component tissues: the nucleus pulpous (“nucleus”), the annulusfibrosis (“annulus”) and two vertebral end plates. The two vertebral endplates are composed of thin cartilage overlying a thin layer of hard,cortical bone which attaches to the spongy, richly vascular, cancellousbone of the vertebral body. The end plates thus act to attach adjacentvertebrae to the disc. In other words, a transitional zone is created bythe end plates between the malleable disc and the bony vertebrae.

The annulus of the disc is a tough, outer fibrous ring which bindstogether adjacent vertebrae. The fibrous portion, which is much like alaminated automobile tire, measures about 10 to 15 millimeters in heightand about 15 to 20 millimeters in thickness. The fibers of the annulusconsist of fifteen to twenty overlapping multiple plies, and areinserted into the superior and inferior vertebral bodies at roughly a 40degree angle in both directions. This configuration particularly resiststorsion, as about half of the angulated fibers will tighten when thevertebrae rotates in either direction, relative to each other. Thelaminated plies are less firmly attached to each other.

Immersed within the annulus is the nucleus. The healthy nucleus islargely a gel like substance having high water content, and like air ina tire, serves to keep the annulus tight yet flexible. The nucleus-gelmoves slightly within the annulus when force is exerted on the adjacentvertebrae while bending, lifting, and other motions.

The spinal disc may be displaced or damaged due to trauma, disease,degenerative defects, or wear over an extended period. A disc herniationoccurs when the annulus fibers are weakened or torn and the inner tissueof the nucleus becomes permanently bulged, distended, or extruded out ofits normal, internal annulus confines The mass of a herniated or“slipped” nucleus tissue can compress a spinal nerve, resulting in legpain, loss of muscle control, or even paralysis. Alternatively, withdisc degeneration, the nucleus loses its water binding ability anddeflates, as though the air had been let out of a tire. Subsequently,the height of the nucleus decreases causing the annulus to buckle inareas where the laminated plies are loosely bonded. As these overlappinglaminated plies of the annulus begin to buckle and separate, eithercircumferential or radial annular tears may occur, which may contributeto persistent or disabling back pain. Adjacent, ancillary spinal facetjoints will also be forced into an overriding position, which may createadditional back pain.

Whenever the nucleus tissue is herniated or removed by surgery, the discspace will narrow and may lose much of its normal stability. In manycases, to alleviate back pain from degenerated or herniated discs, thenucleus is removed and the two adjacent vertebrae are surgically fusedtogether. While this treatment alleviates the pain, all disc motion islost in the fused segment. Ultimately, this procedure places a greaterstress on the discs adjacent to the fused segment as they compensate forlack of motion, perhaps leading to premature degeneration of thoseadjacent discs.

As an alternative to vertebral fusion, various prosthetic discs havebeen developed. The first prosthetics embody a wide variety of ideas,such as ball bearings, springs, metal spikes and other perceived aids.These prosthetics are all made to replace the entire intervertebral discspace and are large and rigid. Beyond the questionable applicability ofthe devices is the inherent difficulties encountered duringimplantation. Due to their size and inflexibility, these devices requirean anterior implantation approach as the barriers presented by thelamina and, more importantly, the spinal cord and nerve roots aredifficult to avoid during posterior or posterior lateral implantationprocedure.

Anterior implantation, however, can involve numerous risks duringsurgery. Various organs present physical obstacles as the surgeonattempts to access the damaged disc area from the front of the patient.After an incision into the patient's abdomen, the surgeon is forced tonavigate around interfering organs and carefully move them aside inorder to gain access to the spine. One risk to the patient from ananterior approach is that these organs may be inadvertently damagedduring the procedure.

In contrast, a posterior approach to intervertebral disc implantationavoids the risks of damaging body organs. Despite this advantage, aposterior approach also raises other difficulties that have discouragedit use. For instance, a posterior approach can introduce a risk ofdamaging the spinal cord. Additionally, vertebral body geometry allowsonly limited access to the intervertebral discs. Thus, the key tosuccessful posterior or posterior lateral implantation is avoidingcontact with the spinal cord, as well as being able to place an implantthrough a limited special area due to the shape of the vertebral bones.Because an anterior approach does not present the space limitations thatoccur with a posterior approach, current prosthetic disc designs are toobulky to use safely with a posterior approach. Therefore, a need existsfor a method of surgically implanting a prosthetic spinal disc into theintervertebral disc space through a posterior approach with minimalcontact with the spinal cord.

SUMMARY OF THE INVENTION

In general, the present invention is directed toward prosthetic discdesigns. In one particular embodiment, an intervertebral artificial discis provided with a first endplate having a plurality of protrusions forattaching to an adjacent vertebrae and an extension portion extendingtowards a second adjacent vertebrae. A second endplate is provided witha plurality of keels for attaching to a second adjacent vertebrae and anextension portion extending towards the first adjacent vertebrae. Aflexible member having an upper portion and a lower portion and a sliderplate positioned within the upper portion of the flexible member is alsoprovided. The extension portion of the first endplate is adapted to fitwithin a first cavity in the upper portion of the flexible member andthe extension portion of the second endplate is adapted to fit within asecond cavity in the lower portion of the flexible member.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a side view of sequentially aligned vertebral bodies, such asare found in the cervical, thoracic and lumbar spine, and a posteriorprosthetic spinal disc located between the vertebral bodies;

FIG. 1B is a top view of one embodiment of a prosthetic spinal disc ofthe present invention;

FIGS. 2A-B illustrate a surgical approach that may be used for insertingthe prosthetic spinal disc of FIG. 1B;

FIG. 3 is a view of a collapsed posterior prosthetic spinal disc thatcan be opened via scissor action;

FIGS. 4A-B are views of a segmented posterior prosthetic spinal disc andits assembly between vertebral bodies;

FIGS. 5A-5D depict various expandable posterior prosthetic spinal discs;

FIGS. 6A-B show open-sided or C-shaped disc implants having a spring;

FIGS. 7A-B show open-sided or C-shaped discs having a flexible portion,curved end plates and stops;

FIGS. 8A-B show open-sided or C-shaped discs having slots that provideflexibility;

FIG. 9 shows a flat, generally rectangular or O-shaped disc having twoslotted side columns;

FIG. 10 shows a flat, generally rectangular or O-shaped disc having anadditional column in the center portion of the disc and slots in theouter columns;

FIG. 11 is an open-sided or C-shaped disc having a coil slot;

FIGS. 12A-B and 13-14 illustrate the use of compressed elements in thepresent invention;

FIGS. 15-26 illustrate the use of varying types interfacing surfaces inthe present invention to achieve or restrict movement in differentdirections;

FIGS. 27-29 illustrate one embodiment of the invention using oblonginserts;

FIGS. 30-45 illustrate the use of stiffness mechanisms, torsion bars,tension and compression springs that may be used in the presentinvention;

FIGS. 46-47 show one embodiment of the present invention utilizing abraided reinforcing material around a balloon or bladder;

FIGS. 48-49 and 50A-B show one example of the present invention;

FIGS. 51-54 illustrate an embodiment of the present invention having afixed IAR;

FIG. 55A, and FIGS. 55B-61 show an example of the present inventionhaving two articulating surfaces;

FIGS. 62A-H, 63A-B, and 64-67 further illustrate prosthetic disc designsof the present invention and the use of a trial and chisel for preparingthe treated area for insertion of disc assemblies;

FIGS. 68-81 illustrate steps used for preparing a treated area forinsertion of a prosthetic spinal disc using a posterior approach;

FIG. 82 is an illustration of one embodiment of a prosthetic disc of thepresent invention;

FIGS. 83A-B illustrate two optional methods for distracting the treatedarea during insertion of a prosthetic disc;

FIGS. 84A-B illustrate selective interaction between a free end of anangled guide and a keyed recess of a trial;

FIGS. 85A-B show one embodiment of a disc assembly holder selectivelyengaged with a disc assembly;

FIG. 86 illustrates one embodiment of a tool used in the methods of thepresent invention;

FIG. 87 illustrates one embodiment of a tool used in the methods of thepresent invention;

FIGS. 88-111 illustrate various tools used in an embodiment of themethods of the present invention;

FIG. 112 illustrates an intervertebral disc space in which paths havebeen cut in vertebral bodies using the methods of the present invention;

FIGS. 113-116 illustrate various tools used in an embodiment of themethods of the present invention; and

FIGS. 117-118 illustrate prosthetic disc assemblies after implantationaccording to the methods of the present invention.

FIG. 119 illustrates yet another embodiment of the prosthetic discassembly according to the present invention.

FIG. 120 illustrates an exploded view of the of the prosthetic discassembly according to the present invention.

FIG. 121 a illustrates cross sectional views of the prosthetic discassembly according to the present invention.

FIG. 122 illustrates a cross sectional view of another embodiment of theprosthetic disc assembly according to the present invention.

FIG. 123 illustrates a cross sectional views of yet another embodimentof the prosthetic disc assembly according to the present invention.

FIG. 124 illustrate two disc assemblies according to the presentinvention.

FIGS. 125 and 126 illustrates the disc assemblies of FIG. 124 positionedin the spine.

DETAILED DESCRIPTION OF THE INVENTION

The present invention relates generally to a posterior prosthetic spinaldisc for replacing a damaged disc between two vertebrae of a spine. Thepresent invention also relates to a method for implanting a prostheticspinal disc via posterior or posterior lateral implantation. Inparticular, the present invention encompasses a method for implantingthe prosthetic spinal disc while avoiding or minimizing contact with thespinal cord.

As described in detail below, the prosthetic spinal disc may bearticulating or non-articulating. In addition, the prosthetic disc maybe formed of one, two, three or more units. For example, two units maybe disposed in the medial-lateral direction at spaced apart locations,and the upper and lower portions of each unit have interfacing surfacesthat forms an arc in the anterior-posterior direction.

If multiple units are used, they may be spaced apart from each other orconnected to prior to insertion in the patient or as they are beingpositioned within the body. The ability to connect the units togethermay allow the prosthetic disc to be inserted using a posterior approachwith less risk of injuring the spinal cord, nerve rootlets, lamina orthe like. In addition, using a plurality of units, either connected ordisposed in spaced apart locations, allows individual units to beinterchangeable with a multiplicity of designs or configurations thatallow the physician to address different physical conditions of thetreated area of the spine and to custom tailor the range of motion thatthe prosthetic disc will permit.

Several embodiments of the invention illustrate different examples ofhow the interfacing surfaces of an articulating prosthetic disc may beformed. For instance, articulation may be accomplished with oneinterfacing surface, such as a ball and joint (see e.g., FIG. 21), oralternatively may be accomplished with two or more interfacing surfacessuch as a core disposed between an upper and lower seating surface (see,e.g., FIG. 1A). The configuration of the surface contact may vary topermit or restrict different types and ranges of motion of the treatedarea. Thus, the contact profile of the interfacing surface may be anarea (such as with a ball and socket configuration), a line (such aswith a roller or sleeve bearing), or a point (such as with a ballbearing).

The materials used for different embodiments of the invention willdepend to some extent upon the type of surface contact being used aswell as the type and extent of wear that may result. Examples ofmaterials that may be used include, but are not limited to polyethylene(or other elastomeric material) on metal, metal on metal, or ceramic onceramic.

The present invention also allows for customization of the instantaneousaxis of rotation (JAR) and/or the center of rotation (COR) of onevertebral body with reference to another. The IAR and COR of a healthyvertebral body with respect to another is constantly changing in allplanes because of pushing, pulling, and tethering of the segment throughits range of motion by the ligaments, annulus, muscles, facets and otherportions of the spine. Often, prosthetic disc replacement designs failto mimic this varying IAR and COR. For example, a fixed ball and sockethas a fixed IAR and COR. One potentially adverse result from using aprosthetic disc having a constrained implant is that the device maycause damage to facet joints due to anatomical interferences that mayoccur with a fixed axis of rotation. On the other hand, in generalconstrained JAR systems have been more stable than past designsutilizing a moving JAR. One example of a prosthetic disc having a fixedJAR is described in U.S. Pat. No. 5,314,477.

Conversely, past devices utilizing a moving IAR have provided theadvantage of allowing for shear translation and of at least partiallymimicking of the moving IAR of a healthy spine. These advantages,however, typically have been achieved in the past at the expense of aloss of stability of the device. Some examples of prosthetic discdesigns having a moving IAR are described in U.S. Pat. Nos. 4,759,766,5,401,269, and 6,414,551.

In contrast, the present invention allows for an implant design that canmimic or partially mimic this varying IAR and COR to the extent desiredby a physician while also preserving stability of the device. Forexample, one embodiment of the invention is a prosthetic disc thatprovides a moving IAR substantially in the sagittal plane so that apatient can more easily flex and extent the spine while limiting themovement of the IAR under lateral bending. It is believed that thisconfiguration provides the best of both worlds by allowing a moving IARfor the predominant or more common motion a patient may undertake inday-to-day life while limiting lateral bending to achieve greaterstability to the device. Several embodiments of the invention permittranslation of one vertebral body with respect to another. By allowingone of these members to translate in the transverse plane results in theIAR and COR also translating in the transverse plane. As explainedfurther below, one additional way of achieving a varying IAR and/or CORin three dimensional spaces is by combining two articulating surfacesopposing one another.

The interfacing surfaces of articulating and non-articulatingembodiments of the present invention also allow for varying degrees ofrotational and linear translation, and several embodiments of thepresent invention likewise permit a similar range of rotation and lineartranslation. Rotational translation is the movement of theintervertebral segment as a result of movement such as flexion,extension, and lateral bending. There are two components in thistranslation: one in the cranial/caudal direction and one in thetransverse plane. Linear translation is translation in the transverseplane as a result of shear forces applied to the intervertebral segment.Thus, a ball and socket mechanism fixed in one location relative to theintervertebral segment would allow only rotational translation but wouldnot permit linear translation. As illustrated in many of the embodimentsthat follow, however, linear translation of a ball and socketconfiguration could be achieved if the ball and socket were able to movein the transverse plane.

Endplates are used to associate the prosthetic disc with the vertebralbodies neighboring the disc. The endplates may be configured in severalways to help ensure a desired endplate-bone interface. For instance, theendplates may have one or more keels that extends into the bony portionof the vertebral body. Over time, bony ingrowths will surround theendplate and further help secure the endplate to the vertebral body.

In addition to keels, the endplate may have other or additional geometrythat helps securely hold the endplate in place. For example, the endplate may have one or more teeth, rails, ribs, flanges, or otherconfigurations that can help provide a surface that can secure theendplate more readily to the bone. Other short-term fixation may includescrews or other fasteners that hold the end plate to the vertebral body.In some embodiments, these fasteners may be removed once a morelong-term interface has been established, or alternatively the fastenersmay remain in place indefinitely or until the prosthetic disc needsadjustment and/or replacement.

In addition to providing an endplate surface geometry or configurationthat may promote bony ingrowths to hold the interfacing surfacestogether securely over the long term, these configurations also may helpprovide short term fixation of the endplate to the vertebral body. Forexample, a keel may have a wedge shape so that the width of a first endof the keel near the endplate is narrower than the width of the distalend. Once installed, the inverted wedge of the keel helps preventseparation of the endplate from the vertebral body at least until bonyingrowths can more securely hold the endplate in place.

To help accelerate and to further promote bony ingrowths at theinterface between the vertebral body and the end plate, the end platemay be coated with an osteoconductive material and/or have a porous ormacrotexture surface. For example, the end plate may be treated with acoating that promotes bone growth. Examples of such coatings include,without limitation, hydroxyl appetite coatings, titanium plasma sprays,sintered beads, or titanium porous coatings.

FIG. 1A is a side view of a posterior prosthetic spinal disc 1 locatedbetween sequentially aligned vertebral bodies 2 and 3, such as are foundin the cervical, thoracic and lumbar spine. Posterior prosthetic spinaldisc 1 conforms in size and shape with the spinal disc that it replacesand restores disc height and the natural curvature of the spine.Posterior prosthetic spinal disc 1 comprises two opposite end plate 5and 7 which are disposed in two substantially parallel horizontal planeswhen it is at rest, i.e., when it is not subjected to any load, eithermoderate or heavy.

The outer faces of end plates 5 and 7 are in direct contact withvertebral bodies 2 and 3 and may be textured or have a plurality ofteeth to ensure sufficient contact and anchoring to the vertebral bodies2 and 3. The outer faces of end plates 5 and 7 may also have a porous ormacrotexture surface that facilitates bone ingrowth so that theposterior prosthetic spinal disc 1 is firmly affixed to vertebral bodies2 and 3. Attached to the inner faces of end plates 5 and 7 are seatingmembers 9 and 11 and a core 13 is securely placed between seatingmembers 9 and 11. A stop member 15 is formed around the equator of thecore 13, which functions to limit the motion of vertebral bodies 2 and 3beyond a predetermined limit that is deemed unsafe to the patient.

As shown in FIG. 1A, the stop member may be formed from a ridge ofmaterial found on the core 13. As the end plates move relative to thecore in response to movement of the spine, the stop member may approachor engage with one or both of the end plates to restrict further motionin a particular direction. The stop member may be formed of a relativelyrigid material so that additional motion is substantially prevented onceengaged against an end plate. Alternatively, the stop material may bemade of resilient material that provides some cushioning or flex fromdeformation of the stop material before the range of motion is fullylimited.

While the stop member is shown in FIG. 1A as being on the core 13, italso may be disposed on one or more of the end plates. For instance, theend plates may be configured with raised areas or ridges on itsperimeter that engage with either the core or the opposing end plate inorder to limit further motion in a particular direction. As mentionedabove, the stop member on the end plate may limit motion to a greaterdegree in one direction than in another. Thus, the stop member may havevarious shapes and thicknesses to provide a variable range in motionthat favors or disfavors movement in particular planes. For example, thestop member may have increased thickness on the side portion of the coreto provide a more limited range of lateral motion of the spine whilestill allowing motion in the posterior/anterior direction.

The motion segment comprises a posterior prosthetic spinal disc 1 andadjacent upper and lower vertebral bodies 2 and 3. The exact contours ofthe core 13, seating members 9 and 11 and stop member 15 determine therange of motion allowed in flexion and extension, side bending, shearand rotation.

FIG. 1B is a top view of a posterior prosthetic spinal disc 1, showingthe top end plate 5 and top seating member 9. The end plates may havevarious shapes that accommodate posterior insertion which avoids contactwith the spinal cord. As shown in FIG. 1B, end plates 5 and 7 may have asubstantially irregular elliptical shape or curved convex portion thatresembles a kidney-shape. FIG. 2A is a top view of a posteriorprosthetic spinal disc 1 being inserted between sequential vertebralbones. The posterior prosthetic spinal disc 1 is guided in place with afirst implant holder 17 via an angled posterior approach that ensuresthat contact with the spinal cord 19 is avoided. The posteriorprosthetic spinal disc 1 is generally oriented in line with thelongitudinal axis of the first implant holder 17. Once the posteriorprosthetic spinal disc 1 safely is maneuvered past the spinal cord 19and in the desired position over the vertebral body 21, the implant maybe turned or rotated, such as from 60.degree. to 120.degree., so that itis oriented at about 90.degree. to the first implant holder 17, as shownin FIG. 2B. Reorienting the implant may be accomplished in many ways.For example, FIG. 2B shows that a second implant holder 23 may beattached on the contra lateral side of the spinal cord to reposition anddistract the implant into its final implanted position. Once theposterior prosthetic spinal disc 1 is in place, the first implant holder17 and the second implant holder 23 is detached from posteriorprosthetic spinal disc 1.

It is preferred that the posterior prosthetic spinal disc 1 closelymimics the mechanical functioning and the various physical attributes ofthe natural spinal disc that it replaces. In some instances, however,the prosthetic spinal disc may permit a more limited range of motion inone or more directions in order to prevent further spinal injury. Ingeneral, the prosthetic spinal disc can help maintain the properintervertebral spacing, allow for proper range of motion, and providegreater stability. It can also help transmit physiological stress moreaccurately.

End plates 5 and 7, seating members 9 and 11, core 13 and stop 15 may becomposed of a variety of biocompatible materials, including metals,ceramic materials and polymers. Such materials include, but are notlimited to, aluminum, alloys, and polyethylene. The outer surfaces ofthe end plates 5 and 7 may also contain a plurality of teeth, maybecoated with an osteoconductive material, antibiotics or othermedicament, or may have a porous or macrotexture surface to help rigidlyattach the end plates to the vertebral bodies by promoting the formationof new bony ingrowth. Such materials and features may be used in any ofthe posterior prosthetic spinal discs described herein.

FIG. 3 is a collapsed posterior prosthetic spinal disc 30 that can beopened via scissor action, in which top end plate 32 and bottom endplate 34 are rotated along a pivot point 36 so that the longitudinalaxes of top end plate 32 and bottom end plate 34 are substantiallyperpendicular. Accordingly, the surface area of the posterior prostheticspinal disc 30 is increased to facilitate greater spinal support. Theposterior prosthetic spinal disc 30 in collapsed form is sufficientlysmall enough to allow for posterior insertion while avoiding contactwith the spinal cord.

FIGS. 4A-B illustrate a posterior prosthetic spinal disc having twosegments for each end plate. The segments may be inserted separatelybetween vertebral bones and assembled or joined together. The firstsegment 40 is inserted between the vertebral bones while avoidingcontact with spinal cord 19. The second segment 42 is subsequentlyinserted between the vertebral bones while avoiding contact with spinalcord 19, and assembled or joined with first segment 40, forming an endplate having larger surface area. The first and second segments may bejoined in any suitable manner to form an end plate. In one embodiment,the first segment has one or more protrusions and/or ridges thatcorrespond to depressions, notches, or teeth in the second segment. Thejoining of the protruding regions of the first segment into thedepressions of the second helps secure the two segments together. Thesame procedure is carried out for the second end plate. The size of theassembled end plates may otherwise be too large to insert betweenvertebral bones while avoiding contact with spinal cord 19.

FIG. 5A is an expandable posterior spinal disc 50 that comprisesexpandable end plates 52 and 54 that can slide open or expand toincrease the perimeter or contact area of the end plate with thevertebral body onto which it resides. In its collapsed state, theexpandable end plate 52 is small enough to insert between vertebralbodies while avoiding contact with the spinal cord. In its expandedstate, the expandable posterior spinal disc 50 has a larger surface areaon upper and lower surfaces 52 and 54, which increases the contact areabetween the expandable posterior spinal disc 50 and the vertebral bones,or at least distributes loading over a greater surface of the vertebralbodies.

The expandable end plate may be formed of two or more segments thatprovide a low profile when in a collapsed state in order to facilitate aposterior approach during insertion. Once it is positioned over thevertebral body, however, it maybe expanded to increase the surface areaof the end plate. The increased surface area helps provide greaterstability of the end plate. Expansion of the end plate may beaccomplished in several ways. In one embodiment, shown in FIG. 5A, afirst segment and second segment may be selectively expanded or slidopen along a substantially linear edge or surface. Thus, when fullyextended the end plate will have a substantially linear slot defined bythe edges of the first and second segment edges.

Alternatively, a portion of the edge of the first and second segmentsmay be curved or rounded as shown in FIG. 5B. In this embodiment, thefirst and second segments may provide more balanced peripheral supportof the core along its edges or sides. For instance, a curved or roundedportion of the first and second segments may help form a lip 66 thatprovides extended support of the core on one side than may be achievedfrom a linear slot. This configuration may help avoid cantilever loadingof the core over the slot or opening between the edges of the first andsecond segments. In other words, lip 66 helps ensure that the connectingportion of the end plate 68 provided more evenly distributed support tothe seat member 70.

The additional lip of expandable posterior spinal discs can have othershapes, preferably being configured to reduce or minimize the occurrenceof cantilever loads. For example, FIG. 5C shows an expandable posteriorspinal disc 72 that comprises expandable end plates 74 and 76 that canexpand along the latitudinal axis and comprises an additional lip 78having a rectangular shape on end plate 74 and/or end plate 76. Inanother example, FIG. 5D shows an expandable posterior spinal disc 80that comprises expandable end plates 82 and 84 that can expand along thelatitudinal axis and comprises an additional lip 86 having a triangularshape on end plate 82 and/or end plate 84. Additionally, a posteriorspinal disc may comprise expandable end plates that can expand along thelatitudinal axis and comprise an additional lip having a convex curve.In both FIG. 5C and FIG. 5D, additional lips 78 and 86 have sufficientoverlap with seating members 79 and 88 respectively that facilitatesreduction of cantilever loads.

FIGS. 6A-B illustrate a non-articulating posterior prosthetic spinaldisc 90 comprising a top end plate 92 and a bottom end plate 94 that arejoined together at one end to form a C-shaped disc. A spring 96 islocated where top end plate 92 and bottom end plate 94 meet or arejoined at one end of each plate 92 and 94 and allow for flexible motionof vertebral bones. The spring can be modified to have various tensionsdepending on the desired range of motion. The portion that joins the topend plate 92 and bottom end plate 94 also may be flexible itself and, inconjunction with spring 96, facilitates motion of the end plates 92 and94. FIG. 6B shows two separate non articulating posterior prostheticspinal discs 90, both of which can be inserted between the same twovertebral bones. The small size of non-articulating posterior prostheticspinal discs 90 allows for easy insertion while avoiding contact withthe spinal cord, and further provides greater freedom of motion becauseeach non-articulating posterior prosthetic spinal disc 90 functionsindependently of one another. In general, the non articulating posteriorprosthetic spinal discs encompassed by the invention have a C-shapeddesign, where openings, slots or springs create flexibility in thematerial to allow motion.

FIG. 7A shows a C-shaped disc 100 having convexly curved end plates 102and 104, flexible portion 106, and stops 108. The outer surface of endplates 102 and 104 may contain a plurality of teeth, may be coated withan osteoconductive material, antibiotic, or other medicament, or mayhave a porous or macrotexture surface to rigidly attach the C-shapeddisc to the vertebral bodies and promote formation of new bone. Theflexible portion 106 is tapered and the amount of taper controls theflexibility of the C-shaped disc. For example, increasing the amount oftaper increases the flexibility of the C-shaped disc. Flexibility mayfurther be controlled by providing a slot 109 located at the flexibleportion 106. The slot may be cut in any shape and oriented in any mannerwithin the flexible portion. The size of the slot may be varied to finetune flexibility. For example, larger slot sizes provide flexibility ofC-shaped discs. In another embodiment, more than one slot may beprovided to increase flexibility. The stops 108 are located at the endopposite of the flexible portion 106 and limit the motion of theC-shaped disc 100. The size of the stops 108, as well as the amount ofcurvature of end plates 102 and 104 may be varied to control the rangeof motion of the end plates before the stops 108 touch. Once the stops108 touch under moderate loads, the curved end plates 102 and 104provide another range of motion under heavy loads that flatten anddecrease the curvature of end plates 102 and 104.

FIG. 7B shows a C-shaped disc having stops 110 that are convexly curvedto provide lateral flexibility. Once the stops 110 touch under moderateload, the curved surface allows the stops 110 to roll in order tofacilitate some lateral spinal movement. The curvature of the stops canbe varied to provide more or less lateral flexibility. In oneembodiment, both stops 110 may be curved. In another embodiment, onestop may be curved while the other stop may be flat, convex, or have adifferent curvature. The stops also can have other surface shapes thatallow for lateral flexibility, such as angled edges. In addition, slotsmay be formed on the lateral sides of the flexible portion to facilitatemovement of end plates 102 and 104 in the lateral plane. The stops alsomay be curved or shaped to allow a greater degree of lateral movement inone direction than in another.

FIG. 8A shows a C-shaped disc 120 having end plates 121 and 122, stops124, and a flexible portion having an opening 126 and slots 128. Stops124 are located at the end opposite of the flexible portion and limitthe motion of the C-shaped disc 120. The size of the stops 124, as wellas the amount of curvature of end plates 121 and 122 may be varied tocontrol the range of motion of the end plates before stops 124 touch.Once stops 124 touch under moderate loads, the curved end plates 121 and122 provide another range of motion under heavy loads that flatten anddecrease the curvature of end plates 121 and 122. The flexible portioncontains slots 128 running through the lateral axis and can have anyshape. The flexible portion also contains an opening 126 that is boredout along the longitudinal axis and helps provide flexibility. Thenumber of slots, the size and shape of the slots, and the size and shapeof the opening enable fine tuning of flexibility, where, for example,increasing the number of slots, as well as increasing the size of theslots or opening, provides for greater flexibility. In one embodiment,the flexible portion may be located closer to the middle of the disc,forming a skewed H-shaped disc, such as illustrated in FIG. 8B. TheH-shaped disc allows for greater flexibility in the anterior andposterior directions. The outer surface of end plates 121 and 122 maycontain a plurality of teeth or be coated with an osteoconductivematerial, have a porous or macrotexture surface to rigidly attach theC-shaped disc to the vertebral bodies, as well as to promote formationof new bone.

FIG. 9 shows a generally oval-shaped or O-shaped disc having end plates131 and 132 and two flexible portions joining end plates 131 and 132 atthe longitudinal ends. Each flexible portion contains slots 136 runningthrough the lateral axis and can have any shape. Each flexible portionalso contains an opening 134 that is bored out along the longitudinalaxis and helps provide flexibility. The number of slots, the size andshape of the slots, and the size and shape of the opening enable finetuning of flexibility, where, for example, increasing the number ofslots, as well as increasing the size of the slots or opening, providesgreater flexibility. Each flexible portion may have the same ordifferent configuration of slot shapes, numbers and sizes, positioning,as well as size and shape of the opening. The flexible portions can alsobe placed near the midline of the disc. In addition, the end plates canhave convex curvature such that at heavy loads, the O-disc can flex bydecreasing the curvature of end plates 131 and 132. The amount ofcurvature can be varied to provide different flexibilities. The outersurface of end plates 131 and 132 may contain a plurality of teeth or becoated with an osteoconductive material, have a porous or macrotexturesurface to rigidly attach the C-shaped disc to the vertebral bodies, aswell as to promote formation of new bone.

FIG. 10 shows a relatively flat double oval or O-shaped disc having anadditional column in the center portion of the disc and slots in theouter columns. The disc has end plates 141 and 142, and columns 144having slots 146 that provide flexibility. With the additional column inthe center of the disc, end plates 141 and 142 will have a lesser degreeof flex when compared to the O-disc described in FIG. 9. Such aconfiguration is desirable in applications where a more rigid disc isrequired. The slots 146 may any shape, size or positioning and as shown,slots 146 are rectangular notches having a cylindrical hole formed atthe inside end of each notch. The outer surface of end plates 141 and142 may contain a plurality of teeth or be coated with anosteoconductive material, have a porous or macrotexture surface torigidly attach the C-shaped disc to the vertebral bodies, as well as topromote formation of new bone.

As shown in FIG. 10, the central column may have a gap or opening wherethe lower portion of the column terminates below the terminus of theupper column. This gap, which in one embodiment can be from about 0.5 mmto about 5 mm, allows the end plates 141 and 142 to have some ability toflex initially until the upper and lower columns meet to prevent furthercompression. In another embodiment, one or more columns may be formedfrom a highly resilient material that can provide some limited motionfollowed by cushioning that increasingly resists further displacement asloading on the prosthetic disc increases.

FIG. 11 illustrates another embodiment of the present invention where aC-shaped disc has two end plates 151 and 152, the posterior ends ofwhich are connected by a flexible portion, and the flexible portion, andthe flexible portion contains a coil slot 156 and an opening 154 that isformed along the longitudinal axis of the disc. The coil slot 156 andopening 154 provide flexibility and can be controlled by varying thesize of the coil slot, number of spirals in the coil slot, as well asthe size and shape of the opening 154. The outer surface of end plates151 and 152 may contain a plurality of teeth or be coated with anosteoconductive material, have a porous or macrotexture surface torigidly attach the C-shaped disc to the vertebral bodies, as well as topromote formation of new bone. Thus, the end plates and flexible portionmay be integrally formed from one material.

In another embodiment of the invention, illustrated in FIGS. 12-14,utilizes a combination of tensioned and compressed elements disposedbetween the upper and lower end plates. The tensioned and compressedelements may be springs, as shown in FIG. 13, or may be made ofresilient material that provides suitable resistance to stretching orcompression. The compression element helps support axial loading alongthe treated vertebral bodies so that their relative positionsapproximate a healthy vertebral body supported by a natural disc.Additionally, at least one tension element helps provide controlledbending or movement of the vertebral bodies relative to each other.

The tensioned or compressed elements may likewise be configured andadapted to allow for compression and translation as shown in FIG. 12.Referring to FIGS. 13 and 14, the compression element can be pivotallyconnected to the upper and lower end plates, thereby allowingtranslation of the end plates in at least one direction by rotating thecompressed element about the pivots. FIG. 14 shows that additionaltranslation can also be provided in a second direction by configuringthe pivoting connection such that the compressed element may slide alonga rod or bar connected to one or more of end plates. As shown in FIG.13, the first and second direction of translation can be generallyorthogonal to each other. In this manner, a limited degree oftranslation permitted in any direction can be accomplished withoutaffecting the range of translational motion in the second direction.

FIGS. 15-20 illustrate another embodiment of the invention including twoor more implants that complement each other to form an arced or curvedsurface in the medial-lateral direction and in the anterior-posteriordirection. FIG. 15 illustrates the curvature created in themedial-lateral direction, while FIG. 16 shows the curvature created inthe anterior-posterior direction. As shown in FIGS. 17 and 18, thecomplementary curved surfaces of the upper and lower portions of theimplants allows the upper vertebral body to move relative to the lowervertebral body while also maintaining a distance between the bodies thatapproximates the height of a natural disc. In one embodiment it ispreferred that the curvature of the implant components is spherical sothat they cooperate and function similarly to a ball and socket.

The implants may be space close together or far apart according tofactors such as the size of the vertebral bodies, the loading that theimplants will undergo, and the range of motion desired. As the implantsare moved either closer together or farther apart, however, thecurvature of the sliding surfaces may be changed. For instance, in theembodiment shown in FIG. 18, the curvature of the upper and lowerportions of the implants in the lateral-medial direction is based on aradius R1 or R2. For implants separated further apart, the radius R2 islarger to account for the increased space between the implants. Changingthe radius R according to the spacing between the implants helpsmaintain a relatively uniform radius of curvature across the full lengthof the implants.

Referring to FIGS. 19 and 20, which are similar in orientation to FIGS.15 and 16, the upper and/or lower portions of the implants may havestops to help limit motion in one or more directions. As shown in FIG.19, for example, medial-lateral movement can be controlled or limited byincluding a stop on one or more sides of an upper or lower portion ofthe implant. As the stop engages with the opposing surface of theimplant, further movement in that direction is restricted.Alternatively, a resilient material may be disposed between the stop andthe opposing surface in order to provide cushioning and to allowresistance to further movement to increase progressively. FIG. 20illustrates that stops may be similarly used on one or more sides of theimplant to limit the range of motion in the anterior-posteriordirection. While the stops in FIGS. 19 and 20 are illustrated protrudingupwards or downwards, other configurations also may be used to create astop or to limit motion. For instance, the sliding surface of theportions of the implants may be prevented from further movement simplyby contacting the end plate of the opposing portion.

FIGS. 21-26 illustrate one embodiment of the invention where differentsurfaces of the prosthetic disc provide for different types of movement.For instance, upper portion indicated as B in FIG. 22 may be configuredso that the interfacing surface permits only lateral bending, while thelower portion A may have an interfacing surface that is a ball or railhaving a radius that can translate for axial rotation.

Normally, during lateral bending the space between one side ofneighboring vertebral bodies becomes larger while the space between theopposite side of the neighboring vertebral bodies gets smaller. Oneembodiment of the present invention helps mimic this characteristic oflateral bending by using a plurality of implants with upper and lowerportions separated by oblong inserts.

As shown in FIG. 28, the oblong inserts are configured within the upperand lower portions of the implants at an angle so that during bendingone insert rotates to help raise one lateral side while the other insertrotates in the same direction to help lower the opposing lateral side.To accomplish this combination of rising and lower of opposing sides ofthe vertebral body during lateral bending, the oblong inserts arepositioned such that the upper ends of the insert are further apart thanthe lower ends

Preferably, the oblong inserts are positioned such that they are angledfrom abut 5.degree. to about 20.degree. from a vertical axis when thevertebral bodies are in a neutral position, i.e., under conditions whenthere is no lateral bending. More preferably, the oblong inserts arepositioned such that the axis from the upper end to the lower end isfrom about 70 to about 130 off of a vertical axis when the vertebralbodies are in a neutral position. As shown in FIG. 27, the insert on theopposing side of the vertebral body is positioned at approximately thesame angle, but at a mirror image of the first insert. In this manner,one side will become lower during lateral binding while the opposingside increases in height.

The amount of increase or decrease in height from rotation of theinserts during lateral bending can be controlled in part by the lengthof the inserts from the upper end to the lower end. Thus, a longerinsert will permit a greater range of lifting or lowering than a shorterinsert. In one embodiment, the length of the insert is from about 3 mmto about 15 mm. In another embodiment, the length of the insert is fromabout 5 mm to about 10 mm.

Additionally, the angle at which the inserts are initially positionedwhen the vertebral bodies are in a neutral position will also affect thedegree to which there is a rise or fall in height from rotation of theinserts during lateral bending. For example, inserts that are angledonly slightly off of a vertical axis will only be able to slightly raiseor lower the height of the sides, whereas increasing the initial angleoff of the vertical axis will allow more significant differences inheight to occur. Thus, it is possible to control the degree of increaseor decrease of height during lateral bending at least by either changingthe length of the inserts or by changing the angle at which the insertsare positioned. For example, for the configuration shown in FIG. 29, theinserts may be positioned such that they are about 100 off of a verticalaxis when the vertebral bodies are in a neutral position. In anotherembodiment, the angle may be from about 3.degree. to about ISO.

As discussed previously, the contacting surfaces of the upper and lowerportions of an insert may be configured to have curved surfaces thatallow varying degrees of lateral-medial movement or posterior-anteriormovement. Stops also may be used to help further control or restrictmovement. In addition to these features, stiffness mechanisms also maybe used to provide greater resistance to movement. FIG. 30, for example,illustrates an upper and lower portion of an insert. A ring of elastomeris disposed in the space where the surfaces of the upper and lowerinsert meet. When compressed, the ring of elastomer adds non-linearresistance.

The use of elastomer to provide non-linear resistance to compression maybe used in a wide variety of configurations in addition to a ring. InFIG. 31, for example, a plurality of elastomer protrusions or nubs 158may be used to add stiffness or non-linear resistance to compression.Skilled artisans would likewise appreciate those other materials orstructures may be used to increase resistance to compression. Forexample, one or more of elastomer nubs or protrusions in FIG. 31 may bereplaced with springs. Further illustration of this embodiment is shownin FIG. 32, where springs and/or elastomer 160 can be placed in tensionat various locations between the upper and lower portions of the insert.

Yet another variation of this embodiment is to use one or more flexiblecantilevers to provide increased stiffness or resistance to compression.Referring to FIG. 33, one or more rods 162 may extend from one portionof an insert, i.e., an upper or lower portion, toward the surface of theopposing portion of the insert. In one embodiment, one end of each rodis fixed to a portion of the insert, but is not fixed to the otherportion of the insert.

Thus, one end is fixed to one portion of the insert while the other endis free to move or bend in response to loading. The free end may be incontact with the surface of the opposing portion of the insert oralternatively may be preloaded by pressing it against the surface of theopposing portion of the insert. In another embodiment, the free end doesnot contact the surface of the opposing portion of the insert until apredetermined amount of movement of one portion relative to the otherhas already occurred.

Once the free end contacts the opposing surface, the bar or rod willbegin to bend in response to additional movement. As the bar bends, thebending forces resist any further movement or compression, and as themovement in a particular direction increases, the resistance increasesas well.

As shown in FIG. 33, the free end may be curved, bent, or otherwiseshaped to prevent or minimize wear of the surface of the opposingportion. The flexibility of each cantilever rod may be altered oradjusted to allow greater or more rapid resistance to motion in onedirection than in another. For instance, cantilever rods placed toresist lateral bending may be more flexible or less resistant tomovement than a cantilever rod used to resist anterior-posteriormovement.

Cantilever rods also may be used to provide controlled resistance torotational movement of the vertebral bodies. FIG. 34 shows a top view ofan insert having this embodiment of the invention. Mechanical stops maybe disposed near the free ends of the cantilever rods so that oncerotation increases beyond a certain point the free end engages with oneof the stops and causes the cantilever bar to bend or resist furtherrotational movement. The torsional resistance created from the stopsincreases as rotation continues.

Another embodiment of the invention utilizes a flexible rod or shapememory metal rod near the center of the insert to provide a stop or togenerate progressive resistance to flexing, extension, lateral bending,or rotation. One example of this embodiment is shown in FIG. 35, whichillustrates a rod connected to a lower portion of an insert andextending upwards into a cavity of the upper portion of the insert. Aswith any of the embodiments described herein, the upper and lowerportions of the insert may be configured to have a ball and socketconfiguration or a simple radius protruding portion and correspondingsimple radius receiving portion, thereby permitting lateral medialmovement, anterior-posterior movement, and rotational movement.

As the upper portion 164 of the insert moves relative to the lowerportion 166, the cavity wall eventually will contact the free end of therod. If the rod is very stiff, contact with the cavity wall will stopfurther movement. In contrast, if the rod is flexible, it may bend inresponse to contact with the cavity wall, thereby providing progressiveresistance to further movement in that direction.

The cross-sectional profile of the cantilever rods described herein maybe any shape, and are not limited to circular cross-sections. Forinstance, the cantilever bars may have a generally rectangularcross-section, such as in FIGS. 37A-C, so that it is more resilient tobending loads in one direction than in another.

Different cross-sectional shapes also may be used to provide resistanceto rotational movement in the embodiment illustrated in FIG. 35. Forinstance, if the cantilever rod has a rectangular cross-section asillustrated in FIGS. 37A-C, and extends into a non-circular cavity,rotational movement can cause the free end of the cantilever to contactthe cavity wall. Once again, the stiffness of the cantilever can bevaried to either prevent further rotation beyond a certain point (i.e.,the cantilever acts as a full stop to further rotation), or thecantilever can flex or twist to provide progressively increasingresistance to further rotation.

In an alternative embodiment (as depicted in FIG. 36A-B), two or morerods may be disposed within the central portion at spaced apartlocations so that rotation causes the plurality of rods to bend andimpart torsional resistance to further rotation. FIG. 38 illustratesanother socket and ball compression mechanism according to theinvention. The hinges may be placed at A to allow the socket and ball to“float”. Under compressive axial loading of the spine, torsion bars 168may bend or flex to cushion the spine.

FIGS. 39-41 show a non-articulating insert according to the inventionhaving two endplates attached to springs, preferably at least 2 or moreindependent springs. The springs allow for motion (translation),compression, and a combination of both (flexion/extension and lateralbending). As illustrated in FIG. 42A (showing an axial view of thespine), a single insert may be used with posterior or posterior lateralimplantation. In addition, two or more inserts may be used, jointly orindependently of each other. For example, FIGS. 42B-C shows two inserts,which may be oriented generally in an anterior-posterior direction or ina medial-lateral direction, whereas FIG. 42D depicts three inserts.Multiple inserts may have the ability to attach to one another afterimplantation.

FIGS. 43-45 illustrate an insert where pivots 170 are added to thenon-articulating insert of FIGS. 39-41. The pivots allow motion, whereasthe springs act as shock absorbers and restore the implant to a neutralposition. The endplates may have teeth, a textured surface, chemicaltreatment, or other means to secure the implant to the vertebral body.

A hollow braid 172 may also be used to make the insert of the invention.As shown in FIGS. 46-47, the braid may be reinforced with metal strutsfor strength and fixation. In addition, the insert may have a hollowpocket 174 filled with a balloon or a bladder of a gel, fluid,elastomer, gas, or other material to mimic the annulus or nucleus. Theballoon may be filled with air or fluid and can have various shapes,e.g., cylindrical, oval, circular, etc.

The following three examples further illustrate how several of thefeatures described above may be implemented in a prosthetic disc.

The first example, shown in FIGS. 48-49 and 50A-B, describes aprosthetic disc that may be designed to have an IAR that is eithersubstantially fixed one location or alternatively may be configured tomove in the axial plane. As shown in FIG. 49, a plurality of upper andlower portions may be inserted at spaced apart locations. Preferably,one upper and one lower portion forms an assembly that can be insertedat the same time. By forming, the disc from two assemblies as shown inthe figures one assembly can be inserted on each side of the spinalcord, thereby greatly reducing the space needed in order to insert thedisc. In this manner, many of the risks commonly associated with aposterior approach can be avoided or minimized.

As explained in detail below, the upper and lower portions may havesegments that can be repositioned after the assembly has been positionedinside the patient in order to bring the interfacing surfaces of theupper and lower portions into their final position.

For example, the upper and/or lower portions may be configured with amovable segment that allows repositioning of the interfacing surfaceonce the portion has been inserted into the patient's body. In thismanner, the overall size of the assembly can be made more compact wheninserting it into the body while also allowing the components of theassembly to be reconfigured once inside the body in order to achieveoptimal positioning of the interfacing surfaces of the prosthetic disc.This, while FIG. 49 illustrates the final positioning of two assembliesafter the segments have been repositioned, the segments initially may beinserted into the body in a low-profile configuration, such asillustrated in FIG. 50A, and then reconfigured to a second position,such as shown in Figure SOB, once in the treated area. The secondposition allows the implant to perform its intended function, while thefirst position provides a low-profile insertion of the assembly. Asshown in FIG. 48, one way to allow repositioning of the segments is toprovide a track on which the segments may slide.

The segments may be configured such that a first assembly may beinserted independently and then interlock with corresponding segments ofa second assembly, as shown for example in FIG. 49. Alternatively, thesegments may be configured such that even after repositioning they donot contact a corresponding segment. In any of these embodiments, alocking mechanism may be used to fix the position of the segmentrelative to the portion it is associated with in order to preventunintended repositioning of the segment after the surgical procedure iscompleted. One example of such a locking mechanism is the use of aprotrusion or detent.

To help minimize the profile of the assembly during insertion, onesegment may be configured such that the assembly has a lower overallheight during insertion than when all of the components of the assemblyare in their final position within the patient. FIGS. 50A-B illustratethis feature of the invention. In particular, the segment associatedwith the upper portion of the assembly is configured such that it slidesalong the interfacing surface of the segment associated with the lowerportion of the assembly. The upper portion may be configured with one ormore tracks or channels that guide a corresponding number of protrusionsor keels on the upper portion of the upper segment. Thus, the uppersegment is able to rotate and slide down the surface of the lowersegment in order to lower the height of the assembly during insertion.Once inside the body, however, the segment can be slid into its finalposition. As this occurs, the overall height of the assembly will beincreased. In one embodiment, the overall height of the assembly may beincreased from about 0.1 mm to about 3 mm, and in another, thedistraction caused by repositioning the segment may be from about 0.5 mmto about 1.5 mm.

The second example of the present invention, illustrated in FIGS. 51 to54, also uses two assemblies and is configured to have a fixed IAR. Theupper and lower portions of the assembly may have interfacing surfacesthat are substantially spherical in curvature and that havesubstantially the same radius of curvature so that the overallconfiguration of the sliding surfaces provides a surface contact over anarea as opposed to a line or point. In this example, the assemblies ofthe upper and lower portions are not configured with slidable segmentsas described in the example above. Because the sliding surfaces in thisexample are substantially spherical in curvature, proper alignment ofeach portion of each assembly is important to achieve a desired surfacecontact over an area instead of a line or point.

The third example of the present invention is shown in FIGS. 55-61. Thisexample uses two articulating surfaces in a three component assembly toprovide a moving IAR in the anterior-posterior direction only. Asdescribed in the examples above, two assemblies may be used to provide alow profile during insertion. Each assembly is formed of threecomponents: an upper portion 176, a lower portion 178, and a centralelement 180 having upper and lower surfaces that interface withcorresponding surfaces of the upper and lower portions. It should beunderstood that the orientation of the surfaces described below may beplaced on an upper or lower component and that the invention is norestricted or limited to only the orientation described below. Oneinterfacing surface is configured in a similar manner as provided inExample 2, above. That is, the interfacing surface is substantiallyspherical in curvature such that the surface contact is over an areainstead of over a line or a point. FIGS. 58A-C illustrate the sphericalsurface interface 184 that may be disposed between the upper portion andthe central element.

The second interfacing surface is formed of two cylindrical surfaces 182that permit rotational sliding essentially in one direction (i.e., aboutone axis). As shown in FIGS. 57A-C, the lower surface of the centralelement has a generally cylindrical shape 182 protruding downward, whilethe lower portion has a corresponding cylindrical shaped groove 182formed therein that receives the cylindrical shape of the centralelement. Preferably, the radii of curvature of both cylindrical shapesare approximately the same such that the surface contact is over an areainstead of a line. In this manner, the cylindrical surfaces can beconfigured to permit bending while restricting rotation. Thus, duringflexion or extension both interfacing surfaces permit movement, whileonly one interfacing surface may permit lateral bending or axialrotation.

In an alternative embodiment, however, a second cylindrical interfacingsurface can be substituted for the spherical surface. This secondcylindrical interfacing surface may be disposed orthogonally to thedirection of the first cylindrical interfacing surface. In this manner,one surface will permit motion in one direction, such as flexion andextension, while the second will permit lateral bending.

FIGS. 59-61 illustrate the types of motion that may be achieved using afirst interfacing surface that is generally spherical with a secondinterfacing surface that is generally cylindrical. FIG. 59 illustrates adisc disposed in a neutral position having a disc height H. Duringextension and flexion, the disc can provide rotational translation inthe axial and in the anterior-posterior direction. Under theseconditions, the overall height of the disc can change. Additionally,however, the disc also permits linear translation without changing theheight of the disc. As shown in FIG. 61, the upper and lower portionscan translate with respect to each other without also having to rotate.

As shown in FIGS. 62A-H, a pair of disc assemblies may be used to form aprosthetic disc of the present invention. One advantage of usingmultiple assemblies is that a posterior approach may be used to positionthem into a treated area. A plurality of disc assemblies having varyingheights, widths, lengths, and ranges of translation and rotationcapability may be provided in a kit to a physician so that the finalselection of the proper disc assembly can be made during the surgicalprocedure. For instance, a plurality of disc assemblies may be providedhaving disc heights varying from about 10 mm to about 20 mm. In oneembodiment, the disc heights may differ by a uniform increment, such asdiffering by about 1 mm or by about 1.5 mm within a range.

Likewise, the length of the disc assembly may be varied to accommodatedifferent anatomies. For instance, disc assemblies may have longitudinalaxes that range from about 20 mm to about 28 mm. Incremental changes inthe length of the assemblies may also be provided in a kit, such as byproviding disc assemblies of different lengths in 2 mm increments. Inanother embodiment, a plurality of assemblies may have at least 2different lengths that differ by more than about 3 mm. For instance, oneset of disc assemblies may have a length of about 22 mm, while anotherset is about 26 mm in length. The length of the disc assembly preferablymay be selected to maximize implant/endplate contact area.

A plurality of assemblies may also be provided with differing ranges ofaxial rotation. For instance, one or more assemblies may have norestriction on rotational movement, or may have stops or other devicesthat prevent rotation only after the rotation has exceeded the range ofmotion of a natural, healthy spine. Some assemblies may limit a range ofaxial rotation to .+−.15.degree., .+−.10.degree., .+−.5.degree., or.+−.2.degree.

Other disc assemblies of the present invention may permit a range ofaxial rotation in one direction, but restrict it in the oppositedirection. In other words, a disc assembly of this embodiment may permitlimited disc rotation so that a patient may rotate or turn their body toone side or in one direction, but not in the other. For example, a discassembly may allow rotation or movement between a 0.degree. position,where the spine is not rotated or turned, to up to about 5.degree., upto about 8.degree., up to about 10.degree., or up to about 15.degree. inone direction only.

As described above, a cylindrical surface may be provided in a discassembly in addition to a second, curved surface corresponding to aportion of a sphere. One feature of this combination of surfaces is thatthe disc can permit translation between the upper vertebral body and thelower vertebral body neighboring the treated area.

In one embodiment, the disc is capable of permitting translation of upto about 3.0 mm in the anterior-posterior direction, while in anotherembodiment the disc is capable of translation of up to about 5 mm. Somedisc assemblies may permit even more translation, such as up to about 7mm or even up to about 10 mm. As illustrated in FIGS. 62A-H anddescribed in depth above, mechanical stops 186 may be provided to limitthe range of motion of the disc assembly. FIG. 62C also illustrates thatspacing of multiple assemblies may be important for providing agenerally spherical surface, if one is desired. For instance, it may bedesirable for the central longitudinal axes of the assemblies to beapproximately 9-16 mm apart, and more preferably from 11-14 mm apart.

The upper and lower portions of a disc assembly may be configured with akeel 188 that can engage with or contact a neighboring vertebral body.One advantage of providing a keel is that it may be used to guide theassembly into position during insertion into a treated area of thespine. For instance, as illustrated in FIGS. 63A-B and 64-65, a channelor groove may be cut out of a vertebral body next to the treated area.Then, a physician may insert the assembly into the vertebral body sothat the keel slides in the groove or channel. The keel and grove orchannel may be substantially linear or straight, or alternatively, maybe curved or arched so that the assembly rotates and slides intoposition.

The use of one or more keels may also increase bone to implant surfacecontact, thereby decreasing the likelihood that the assembly will shiftor move about of position. In one embodiment, the increase in surfacecontact may be about 5% or more, which in another embodiment theincrease may be about 15% or more.

The cross-sectional profile of the keel may have different shapes. Forinstance, the cross-sectional profile of the keel may have the shape ofa wedge, a truncated wedge, a rectangle, or a square. As shown in FIG.63A, the channel or groove may be cut to have a cross-sectional profilecorresponding approximately to the shape of the keel. One advantage ofthe keel having a truncated wedge cross-section is that a similarlyshaped channel or groove may ensure that the keel engages with the bonysurface. This configuration may also provide increased resistance toexpulsion of the disc assembly.

Over time, it is believe that the stability of the disc assembly in thetreated area will further increase as bone growth engages with outersurfaces of the disc assembly. To facilitate this growth and increasedstability, all or part of the surfaces of the disc assembly that engagesor otherwise contacts bone may be treated to promote bony on growth. Forinstance, titanium plasma may be provided on the keel or other portionsof the assembly to provide a matrix for bone growth. In addition, thekeel may be configured with notches, slots, or openings formed along itslength. As bone grows into these openings, the disc assembly will becomemore securely anchored in place.

As a disc assembly is first inserted into a treated area, it may need tobe repositioned, rotated or otherwise moved. For instance, repositioningthe disc assembly may be needed so that the keel can properly engagewith the channel or groove. As shown in FIG. 62G, the leading edge Le ofthe disc assembly may be configured without a keel. Thus, in oneembodiment the assembly can be partially inserted into the treated areawithout the keel engaging with or contacting the vertebral body. In oneembodiment, the length of the leading edge is from about 1 mm to about10 mm, while in another embodiment the leading edge is from about 2 mmto about 5 mm. Alternatively, the length of the leading edge may be fromabout 1% to about 20% of the length of the component on which it isdisposed, or may be from about 2% to about 10%. The length of thecomponent may be determined by measuring the longitudinal central axisof the portion or component on which the leading edge is disposed.

In addition, referring again to FIG. 620, the keel may have an initialportion that is sloped or gradually increases in height. Providing aramped portion may aid in aligning and inserting the keel into a grooveor channel formed in a vertebral body.

The present invention also encompasses a method for implanting aposterior prosthetic spinal disc. In particular, the method comprisesremoving a defective vertebral disc using conventional methods andinstruments; separating or distracting adjacent vertebral bodies topermit insertion of the posterior prosthetic spinal disc; inserting andpositioning the posterior prosthetic spinal disc using a posterior orposterior lateral insertion that avoids contact with the spinal cord;and relieving the separation or distraction of the adjacent vertebralbodies.

As will be explained in detail below, there are several variations inwhich the present invention may be used to provide a replacement orprosthetic disc for a patient that restores or maintains a more naturalrange of motion. While a single disc assembly may be used to establishthe artificial disc within a patient, it may be preferred in some casesto provide more than one artificial disc assembly. Vertebral bodieshaving larger sized endplates, for instance, may benefit from using twoor more disc assemblies, or subassemblies to create an artificial discin a treated area. For example, a disc assembly that is from about 9 mmwide may only need an insertion window that is from about 9 mm to about11 mm of wide. In one embodiment, the insertion window needed to deploya disc assembly is from about 7 mm to about 15 mm wide, and morepreferably is from about 9 mm to about 12 mm wide.

Several benefits may be realized from using multiple disc assemblies.For instance, one result of using multiple assemblies may be that thesmaller insertion windows may not require as significant motion orretraction of the aorta or vena cava. For example, in one embodiment,movement of the aorta in the present invention for inserting one of aplurality of disc assemblies is less than half the distance ofrepositioning that would be required if the prosthetic disc were made ofa single, full size assembly. In addition, using multiple discassemblies may allow a shorter duration of time during which the aorta,vena cava or other anatomy is moved out of its natural position. In oneembodiment, for example, the duration of time that the aorta or venacava is moved for inserting one or a plurality of disc assemblies isless than half of the duration of time normally required to insert aprosthetic disc made of only one assembly or unit. In addition, thesmaller insertion windows that can be achieved from using multiple discassemblies will likely make it easier to access the disc space from aswell as allow for greater options in the approaches that may be used.

Furthermore, the use of multiple assemblies may reduce the frequencyand/or the amount of retraction needed during insertion and positioningof the assemblies. For example, if two disc assemblies are used in aposterior approach, a central region of the treated area in theanterior-posterior direction may have sufficient space for placing adistractor. As a result, other benefits from this configuration may alsobe achieved. For instance, in many embodiments of the invention it maybe useful to ensure that the prosthetic disc is positioned properlyalong the midline of the vertebral body in the anterior-posteriordirection. By using a distractor in the central region of the treatedarea, the present invention may allow a physician to select a midline ofthe prosthetic disc with respect to the vertebral body, distract thevertebral bodies with the distractor in the central region, conduct anx-ray or other procedure to confirm that the selected midline of theprosthetic disc is approximately the same as the midline of thevertebral body, and make any desired adjustments of the distractorlocation before inserting a disc assembly. In one embodiment, thephysician's selected location of the midline of the prosthetic discdiffers from the midline of the vertebral body by less than about 3 mm,and more preferably differs by less than about 1 mm at any point alongthe length of the part of the distractor located between the vertebralbodies. If the difference between the selected location of the midlineof the prosthetic disc and the confirmed midline of the vertebral bodyfalls outside an acceptable tolerance, the physician may then repositionthe distractor and either reconfirm its new position or continue withinserting the disc assemblies after the adjustment is made. Once thedistractor is in an acceptable or desired position, the disc assembliesmay then be placed within the treated areas. The distractor location maybe used with or without other tools or devices to help ensure correctplacement of the assemblies with respect to the anterior-posteriormidline of the vertebral bodies.

A disc assembly may comprise tree component parts: an upper rigid plate,a lower rigid plate, and a central core or core element. The coreelement is disposed generally between seating surfaces of the upper andlower plates. The seating surfaces of each plate may be contoured toprovide a desired range of motion. For example, one or more of theseating surfaces may have a substantially spherical curvature. In thismanner, the seating surface may generally correspond to a portion of aball or a socket. The central element may likewise have a contouredsurface that generally has the same curvature as the seating surface itcontacts. Thus, a spherical-shaped seating surface can receive orcontact a portion of the central element having a spherical contourhaving a similar radius of curvature. The contact between the twosurfaces may therefore correspond to a portion of a ball and socket.

Providing a spherical surface allows the two components to rotate andslide across the contacting surfaces in a manner that would permitbending and rotation ozone vertebral body relative to another. If thesetwo contacting surfaces were the only elements allowing movement, theIAR of the disc would be constant. Providing a second contacting surfaceallows the disc to mimic a variable JAR of a healthy disc. For example,a second contacting surface between the second rigid plate and thecentral element may have a cylindrical contour, preferably allowing thecore element to provide rotation in the anterior-posterior direction.Thus, it is preferred that the cylindrical surfaces of the second rigidplate and core element have an axis of rotation that extendsapproximately in a lateral direction.

The combination of a spherical shaped surface contact between one plateand a portion of the core element with a second generally cylindricalcontacting surface between another plate and another portion of the coreelement allows the disc to have a variable JAR. This configuration alsoallows for translation ozone vertebral body relative to anothervertebral body without requiring either vertebral body to rotate andwithout requiring the distance between the vertebral bodies to increaseor decrease.

The curvature of the seating surfaces of the plates may be concave andthe corresponding contoured portions of the core element may be convexto provide contact between the surfaces. Alternatively, one or more ofthe contoured surfaces of the core element may be concave and theseating surface for which it engages likewise may be inverted. Forexample, in one embodiment the core element may have a contoured convexsurface that it semi-spherical or generally corresponds to a portion ofa spherical surface, and a contoured concave surface that issemi-cylindrical or generally corresponds to a portion of a cylinder.One advantage of this configuration is that is may be capable ofachieving a lower overall height than a core element having two convexcontoured surfaces.

As described previously, more than one assembly may be used to form adisc. For example, a second assembly may be provided having a similararrangement of plates and a core element. When disposed in a treatedarea, one or more components of an assembly may contact or eveninterlock with a corresponding component of another assembly. Forinstance, the seating surfaces of plates disposed on the bottom of twoassemblies may be independently inserted into the treated region andsubsequently joined. Conversely, the assemblies may be disposed at apredetermined distance from the other. For example, if two or moreassemblies have contoured semi-spherical surfaces with a large radius ofcurvature, the assemblies may be separated by a predetermined distanceso that the two contacting surfaces operate as component parts of a balland socket configuration.

The configuration of the contacting surfaces of the disc may be varieddepending upon the surgical approach used to insert the assembly. Forinstance, in one embodiment a facet capsule may be removed from one sideof a vertebral body to provide access to the treated area from atransforaminal approach. The endplates of the vertebral bodies in thetreated area may then be cut or otherwise prepared for receiving anassembly. Preferably, the bony anatomy of the vertebral body thatdefines the vertebral foramen still encloses this region after theremoval of the facet capsule. Once the treated area is prepared, anassembly may be inserted. In addition to a posterior or transforaminalapproach, other approaches can be used with the present invention,including, but not limited to posterior-lateral, lateral, or anteriorapproaches.

With a transforaminal approach, the direction or path in which theassembly is inserted may form an angle with an axis extending in theanterior-posterior direction. Because the approach to the treated areais at an angle, the seating surfaces may be configured to provide adesired functionality. For example, as described above, the assembly mayhave a cylindrical seating surface having an axis that extends generallyin a lateral direction of the spine. Thus, the plates of the assemblymay have a longitudinal axis that generally corresponds to the path inwhich the assembly is inserted, and the axis of rotation of thecylindrical contoured surface of the core element may form an angle fromabout 20.degree. to about 70.degree. of the longitudinal axis. Morepreferably, the angle between the longitudinal axis of the plate and thecore element axis of rotation forms an angle from about 30.degree. toabout 60.degree.

When a facet capsule is removed, the rotational stability of thevertebral body may be compromised. Since anatomy that helps preventexcessive rotation of the vertebral body is removed, it may bebeneficial to provide a mechanical stop that prevents rotation in thecompromised direction. In one embodiment, the stop only permits rotationof less than 10 degrees in one direction, and more preferably preventsrotation greater than 7 degrees. In other embodiments, the stop onlypermits rotation from about 1 to about 7 degrees or from about 1 toabout 5 degrees in one direction. If the facet capsule on the opposingside of the vertebral body is still intact, it may not be necessary toprovide a mechanical stop for rotation in the opposite direction. Inthis manner, a rotational stop may be provided only when anatomy aidingin this functionality has been removed.

It is preferred that the contact between the seating surface of a plateand a contoured surface of a core element extends over an area ratherthan a line or a point. More preferably, all contact surfaces of theinvention extend over an area. However, if a convex surfacesemi-spherical surface were formed with a smaller radius of curvaturethan the corresponding concave surface, it would be possible to have thecontact between the two surfaces correspond to a point contact.Likewise, a convex cylindrical surface may be formed to be smaller thanthe concave cylindrical surface it engages with in order to form acontact surface corresponding to a line.

The plates also may be configured to engage more securely with thevertebral bodies that they contact. For instance, one or more raisedridges or keels may extend at least partially into the endplate of thevertebral body. The vertebral body likewise may be prepared by cutting asimilar number of grooves or channels that will receive the keels. Thegrooves or channels may help guide the assembly into proper position inthe treated area. This feature may be particularly beneficial when acertain orientation of the assembly relative to the vertebral body isdesired.

The ridges or keels and corresponding channels or grooves also may bestraight or curved to match the desired insertion path of the assembly.In one embodiment, the cross-section of a ridge or keel may betriangular or have a truncated triangular shape. As mentioned above, ifmore than one assembly is being used, it may be desirable for theassemblies to be separated by a predetermined distance. The grooves orchannels formed in a vertebral body may help achieve the properorientation and distance of the assemblies.

To date, no tool or device has been developed that can provide thesefeatures to ensure proper insertion of a multi-assembly artificial disc.As shown in FIGS. 63A-B and 64-65, a trial 190 may be used to accuratelyform channels or grooves at a predetermined distance. Turning to FIG.64, a trial 190 may be used to aid in cutting upper and/or lowerchannels in facing endplates of two vertebral bodies. Additionally, thetrial may smooth portions of the endplate surfaces where an assembly maytravel or ultimately be disposed. The trial may be inserted in adirection that corresponds to the path that will be used to insert theassembly. As mentioned above, the insertion path of the assembly may notalways correspond to anterior-posterior axis of the vertebral bodies.For instance, an angle formed between the direction of the insertionpath for the assemblies and the anterior-posterior axis may be fromabout 20.degree. to about 70.degree., or may be from about 30.degree. toabout 60.degree. The path also may form a circular arc having a radiusof curvature corresponding to the curvature of the ridges or keels ofthe plates. In this manner, the assembly may be rotated or turned intoits final position as it moves along the channels or grooves.

Once the first channel and groove or plurality of channels and grooveshas been formed, a guide 192 may be used to determine where a second setof channels or grooves may be formed. In general, the guide 192 is incommunication with and extends from the first trial 190. As shown inFIGS. 63B and 64-65, the guide 192 may be disposed within a centralportion of the trial 190. Once the trial is in its proper position, theguide may then be deployed a predetermined distance. Turning to FIG. 65,a portion of the free end of the guide may have a configuration that canreceive a second cutting tool 194. The second cutting tool 194 may thenbe used to form a second plurality of grooves or channels and to preparea second region of the treated area to receive a second assembly. Theguide 192 and trial 190 may then be removed and the assemblies insertedinto the treated area.

The plates used to contact with the endplates of the upper or lowervertebral bodies of the treated area should have sufficient size todistribute loading over an area of the vertebral body to prevent failureof the endplates. Thus, one or more of the rigid plates may have alength from about 25 to about 32 mm, and more preferably from about 28to about 30 mm. Likewise, the width of one or more plates may be fromabout 10 to about 18 mm, and more preferably is about 12 to abut 14 mm.

In another embodiment illustrated in FIGS. 66-67, a trial may be capableof connecting with a handle having a detachable grip. In one embodiment,the trial may have a chisel guide 196 and keyed recess 198. This tool,among others may be used to facilitate installation of one or more discassemblies from a posterior approach in the following exemplary manner.

As shown in FIG. 68, a physician may first perform a discectomy in thetreated area. In one embodiment, the discectomy is performed so that aperimeter region of the annulus is not removed. For instance, 1 mm to 7mm, and more preferably 3 mm to 5 mm, wide region along the perimeter ofthe anterior side of the vertebral body may remain after the discectomyis completed.

When viewed from the posterior side, the spinal cord may obstruct theview of a central portion of the vertebral bodies thereby leaving twoposterior sides of the vertebral body for inserting disc assemblies. Ifdesired, a distractor may be used on the contralateral side while atrial is inserted on the other side. When a posterior approach is used,a preferred embodiment of the invention is to use 2 disc assemblieswhere one is placed in the treated area from one side of the spinal cordand the other is inserted from the other side.

In another embodiment, the trial itself may be used to distract thevertebral bodies. The physician may assess the treated area and select asuitable disc a suitable disc assembly from a plurality provided in akit. Factors that may be considered when selecting a disc assembly mayinclude, among others, the footprint of the disc assembly, lordosis,disc assembly height, and size.

As shown in FIG. 62C, if one or more sliding surfaces of the prostheticdisc is substantially spherical in curvature, it is desirable toposition the disc assemblies a predetermined distance apart from eachother and in proper alignment to allow portions of the 2 disc assembliesthat form the sliding surface to cooperate. Providing a keel on eachdisc assembly may be useful for properly separating (if needed) andaligning each assembly with respect to each other and possibly also withrespect to the treated area. For instance, 2 disc assemblies may beconfigured such that a keel on one assembly should be approximately 13mm from the center of a keel on the second disc assembly. The distancebetween keels may be varied to account for differences in the radius ofcurvature of the sliding surfaces, the location of the keel on each discassembly, the condition of the anatomy in the treated area, and thelike.

While the precise distance between keels does not need to be specified,the physician should understand how to align and position the discassemblies. For instance, the distance between keels for properalignment may be selected from a range from about 5 mm to about 20 mm,or from about 10 mm to about 15 mm, and the selected distance may thenbe provided to the physician or accounted for in the tools provided tothe physician.

In one embodiment, each of the two disc assemblies is positioned andaligned a predetermined distance from the midline of the vertebral bodyin the anterior-posterior direction. For instance, as shown in FIG. 71,the trial may be inserted into the treated area on one side of thespinal cord such that the center of the chisel guide, when properlypositioned, is from about 3 mm to about 10 mm from the midline of thevertebral body. More preferably, the center of the chisel guide whenproperly positioned is from about 4 mm to about 8 mm from the midline ofthe vertebral body.

Once the trial is in its proper position, the grip of the handle may beremoved. Preferably, the handle is formed oat least a detachable gripand a shaft in communication with the trial. When the grip is removed,the shaft may then be used as a guide rod for additional tooling andinstruments.

For example, once the grip is removed, the shaft may be used as a guidefor applying a chisel to form grooves or channels in the treated area.More specifically, with reference to FIGS. 70-72, a chisel 200 may beprovided that can slidingly engage with the shaft of the handle to helpensure that the chisel is positioned properly for forming a channel orgroove in one or both vertebral bodies adjacent to the treated area. Inone embodiment, a portion of the chisel 200 forms a tube 206 or aperturehaving a cross-section corresponding approximately in the cross-sectionof the handle shaft. The tube or aperture may be slightly larger toallow the chisel to move more easily along the length of the shaft.

As shown in FIG. 70, the end of the chisel that impacts against, cuts orotherwise contacts the vertebral bodies has chisel blades 202 that maybe shaped and configured to form grooves or channels in the vertebralbodies of a desired shape. Thus, in one embodiment, the cross-sectionedshape of the chisel blade is a truncated wedge. In one embodiment, thecross-section of the chisel blade may be approximately the same as thecross-section of the keel of the disc assembly. The end of the chiselopposite the chisel blade may have an enlarged impaction face 204. Thus,the physician may align and position the chisel blades 202 against oneor more vertebral bodies neighboring the treated area and strike theimpaction face 204 to drive the blades into the vertebral bodies. As thechisel blades are worked into the treated area, the blades may be guidedand maintained in proper position by slidingly engaging with the chiselguide 196 formed on the trial. Preferably, the length of the chisel maybe selected such that the chisel blades have progressed to their desiredposition when the impaction face is flush with the handle shaft.

In one embodiment, the chisel blade may be selectively detached from thechisel. As shown in FIGS. 72-74, for example, the impaction face 204 andchisel tube 206 may be separated from the chisel blades and removed.Likewise, the trial may be selectively detached from the handle shaft.Thus, it is possible to remove these components of the instruments andleave the trial and chisel blade in the treated area, as shown in FIG.74.

Turning to FIG. 75, with the trial and chisel blades remaining inposition, the spinal cord may be repositioned or moved slightly toprovide access to the contra-lateral side of the treated area. Aspreviously discussed, the trial may be configured with a keyed recess198. The keyed recess 198 is positioned so that it faces toward thecontralateral side of the treated area (i.e., toward the midline of thevertebral body in the A-P direction). Alternatively, the trial may beconfigured with two keyed recesses 198 formed on opposing lateral facesof the trial. This configuration would permit the trial to be insertedon either side of the spinal cord. As shown in FIG. 76, an angled guide208 may then be inserted into the treated area on the contra-lateralside of the area from the trial and chisel blade. Preferably, the angledguide comprises an angled head 210 and a shaft 212 that is substantiallystraight. Thus, the shaft 212 may be substantially parallel to thelongitudinal axis 214 of the chisel blades when the angled guide isproperly connected into the keyed recess.

The angled guide may be selectively engaged with a keyed recess of thetrial so that is may be attached or removed as desired. Preferably, theangled guide is only capable of engaging with the keyed recess at oneangle and orientation. In other words, the angle with which the angledguide is inserted into the keyed recess is predetermined and known. Insome embodiments, the angled guide and the keyed recess may havecomplementary surfaces that allow a surgeon to determine when the angledguide has been fully inserted into the keyed recess. Once the angledguide is in communication or proper registration with the keyed recess,the shaft extending outward of the treated area may then be used toinsert a second chisel blade into the treated area. As shown in FIG. 76,the cross section of the shaft of the angled guide may be generallyoval, but it also may be rectangular, square, triangular, oblong,elliptical, or have some other shape that helps prevent rotation of achisel blade as it is being inserted. Of course, it is preferable thatthe second chisel blade has a tube or aperture corresponding generallyto the shape of the cross-section of the angled guide. Preferably, thesecond chisel is substantially the same size as the first. The blade maythen be placed on the shaft of the angled guide and positioned near oradjacent to the vertebral bodies. A chisel tube and impaction face mayonce again be employed to drive the chisel blade into the treated area.

One advantage of engaging the angled guide with the keyed recess is thatthe chisel blades into the contra-lateral side of the vertebral body maybe inserted at a known distance away from the first set of chiselblades. Another advantage of using the angled guide may be that thechisel blades on the contra-lateral side of the vertebral body may beinserted substantially parallel to the first set of inserted chiselblades. In one embodiment, the angled guide is preferably configured anddimensioned such that the chisel blades on the contra-lateral side areinserted between about 8 mm and about 16 mm away from the first set ofchisel blades. More preferably, the chisel blades on the contra-lateralside are inserted between about 10 and about 15 mm away, and mostpreferably, the chisel blades on the contra-lateral side are insertedbetween about 12 mm and about 14 mm away from the first set of chiselblades.

Once the chisel blade has been fully placed or inserted into in thecontra-lateral side of the treated area, it may then be removed from thetreated area along with the angled guide. In one embodiment, both thechisel blade and angled guide are removed at the same time (i.e., theangled guide may be removed with the chisel blade still disposed on theshaft). As shown in FIG. 78, a disc assembly 216 may then be deployedinto the contra-lateral side. To facilitate insertion of the discassembly 216, an implant holder 218 may be used to securely grip theassembly until its keels are inserted into the grooves or channelsformed by the chisel. FIG. 78 illustrates one embodiment where theimplant holder may selectively engage with the rear-most or posteriorside of the disc assembly. As shown in FIGS. 62A and 78, rearward endsof the upper and lower portions of the assembly may have receptacles 220that allow the holder to securely grip the assembly. In addition, hookedtips 222 formed on the holder may selectively engage with the assemblycomponents. Configuring the disc assembly and implant holder in thismanner allows the overall height and width needed for insertion of thedisc assembly to remain at a minimum.

Alternatively, the implant holder 218 may engage with the outermostupper and lower surfaces of the disc assembly, on either side of thekeels. However, this configuration may require the vertebral bodies tobe distracted during insertion, thereby potentially causing the firstchisel blade and/or the trial to become dislodged from their positions.Additionally, an implant holder may grip the disc assembly from thelateral sides; however, this too may require an increase in the overallsize of the window or opening needed in order to insert the discassembly. Thus, while the use of these alternative embodiments may fallwithin the scope of the invention, some may have disadvantages.

Once the keels of the disc assembly have begun to be positioned on overthe channels or grooves, the implant holder may be used to push the discassembly into the treated area. As the disc assembly nears its finalposition, resistance between the vertebral bodies and the surfaces ofthe disc assembly may significantly resist further progress. If desiredor needed, gentle impact forces may be applied to the implant holder toaid in moving the disc assembly into position.

The first chisel blade and trial may then be removed and a second discassembly inserted in a similar manner. In particular, the chisel blademay be operatively connected with the chisel tube or another instrumentand then withdrawn from the body. Likewise, the handle shaft, andoptionally the grip, may be reconnected to the trial so that it too canbe withdrawn. The removal of the trial and chisel blade can be performedat the same time or sequentially. Once the trial and chisel blades havebeen removed, the second disc assembly may be inserted. FIGS. 68-80generally illustrates how two disc assemblies may be inserted from aposterior approach into their desired positions.

As mentioned previously, the keel of a disc assembly may be configuredto promote or permit bony ingrowth that may help hold the disc assemblyin place more securely. FIG. 82 illustrates one embodiment of a keelhaving a plurality of slots or cuts formed in it. FIGS. 62E and 62H alsoshow other examples of slotted keels. Returning to FIG. 82, the slots orcuts may extend at an angle, such as from about 5.degree. to about40.degree. off from a vertical direction, and more preferably from about10.degree. to about 30.degree. A keel may have two or more, or eventhree or more slots or cuts. One skilled in the art would appreciatethat other configurations may also be used to promote bony ingrowth thatmight help further secure the disc assembly in place. For instance, thekeel may have holes or apertures drilled into it, longitudinal orhorizontal slots may be formed, and the sidewalls of the keel may betextured with one or more grooves or channels that does not extend fullythrough the keel to the opposing sidewall.

In addition, the face of the keel that first inserted into a groove orchannel may have a taper or chamfer. One potential advantage ofconfiguring a keel with a taper or chamfer on its face is that it mayassist in aligning the keel with the opening of the channel or groove.In addition, a chamfered or tapered face may help reduce drag forces andundesired cutting or gouging of the channel or groove as the keel ispushed toward its final position.

One advantage of providing multiple assemblies to form the artificialdisc is that it allows the assemblies to be placed into position withoutsignificant vessel retraction. Thus, insertion from the anterior of thevertebral bodies can be achieved with minimal repositioning of the venacava or aorta. Because the wall of the vena cava is a thin, it puncturesor tears more readily than other vessels.

Conversely, the wall of the aorta is thicker than the vena cava, andtherefore more resistant to tearing or punctures, but the pressure ofthe blood supply is considerably higher. As a result, damage to theaorta can result in significant blood loss. Therefore, one benefit of amulti-assembly artificial disc is the reduced need to disturb or movethese major blood vessels.

Another advantage to using a multi-assembly configuration is that itpermits a physician to adjust or replace one or more assemblies from adifferent approach than used during the original insertion of the disc.When an implant is placed in a region of the spine, a region surroundingthe area of insertion can become obscured or blocked by scar tissue thatgradually forms after the procedure. This scar tissue can also bind toneighboring anatomy, including the major blood vessels so that it isextremely difficult to reuse the insertion window again withoutsubstantial risk to the patient.

When multiple assemblies are used, however, it is possible to use asecond approach to adjust, remove, or replace the artificial disc. Forinstance, if disc assemblies are inserted into position from theanterior side of the vertebral body, it would be possible to remove oradjust the assemblies using a posterior approach using the methods,tools, and techniques described herein. Likewise, a multi-assemblyartificial disc can be inserted from a posterior direction, therebyleaving the anterior side available for future access to the disc.

In some instances, it may be desirable to use a second approach toadjust, remove, or replace an artificial disc at a later time. Forexample, a disc may be inserted during a first surgery. Normal bodymovement over a period of time may then necessitate adjustment of theartificial disc. The present invention allows a surgeon to re-enter thevertebrae using a second approach. The second approach may be done atany desired time. For example, a second surgery using a second approachmay be performed about six months or more after the first surgery. Morepreferably, a second surgery using a second approach may be performedabout one year or more after the first surgery. Most preferably, asecond surgery using a second approach may be performed about five yearsor more after the first surgery.

As discussed previously, where more than one implant or assembly isinserted into the intervertebral space, precise placement of each insertmay be desired. Because the articulating surface of each assembly reliesor cooperates with the articulating surface of its correspondingassembly, precise placement of the assemblies is preferable. Moreparticularly, precise placement refers to the placement of one assemblysuch that it is aligned and spaced apart from the other assembly orassemblies in such a way that each articulating surface of therespective assemblies may cooperate with each other to form an effectiverange of movement as if there were a unified articulating surface. Forexample, with respect to the embodiment disclosed in FIGS. 86 to 110,precise placement means that each keel of each assembly lie parallel toeach other. Additionally, each assembly would be spaced apart from theother assembly such that each independent articulating surface allowsthe articulating surface of its corresponding assembly to act as ormimic one complete surface, i.e. one semispherical articulating surface.In one particular embodiment, each assembly should be inserted at aproper predetermined depth within the intervertebral space, and eachassembly should be inserted generally to the same depth. In assuringsuch precise placement, methods and tools have been developed inaccordance with the present invention for ease of implantation andaccuracy. Furthermore, in controlling each of these positioningvariables, a surgeon should be careful during the entire procedure toavoid contact with the spinal cord while working within confined spaces.

In an exemplary embodiment of the present invention, methods and toolsare provided for inserting more than one assembly of a prosthetic disc.The methods and tools relate to positioning a second implant based onthe position of a first implant. As discussed previously, any number ofmethods may be used to position a second implant based on the positionof the first implant. As used herein, “based on” means the positioningor placement of a second object, path, cut, or other item as determinedby a position or placement of a first item. In the embodiment describedbelow, the positioning of a second implant may be accomplished by usinga path cut by a first chisel to determine the path cut by a secondchisel.

In general, prior to insertion of the prosthetic disc, theintervertebral space is prepared. In one variation, a surgeon performs alamenectomy or laminotomy to remove all or part of the lamina. Thisprocedure is used to create a “window” through which the surgeon mayaccess the intervertebral space. In some instances, a surgeon mayperform a total discectomy, in which the disc between two vertebrae isremoved. Alternatively, a surgeon may perform a partial discectomy, inwhich only a portion of the disc is removed. Partial discectomiestypically leave a portion of the annulus of the disc intact on theanterior portion of the intervertebral disc space. The present inventionis not limited to any particular type of discectomy, whether complete,partial or otherwise.

In one embodiment, another step in the process of inserting a prostheticdisc according to the present invention may include preparation of theupper and lower surfaces of the vertebral bodies. In this step, asurgeon may scrape the upper and lower surfaces of the vertebral bodies.Scraping the surfaces may cause some bleeding, which may improve thechances of bony growth into the inserted assemblies.

In another embodiment, the disc space is prepared by inserting varioustools to help loosen the muscles and ligaments that keep the disc spacetogether. In this embodiment of the present invention, a paddledistractor may be used. With reference to FIG. 86, a paddle distractor250 is provided. Paddle distractor may have a handle 252 that isattached to an elongated shaft portion 254. At the end of elongatedshaft portion 254 the paddle distractor has an area shaped as a paddle256, or an area that is wider than its thickness. The length of paddlearea or paddle head 256 may vary, although one of skill in the art wouldrecognize that said length would be sized appropriately so as to enterthe intervertebral space without interfering with surrounding tissue orother internal body parts. The shape of the paddle area allows a surgeonto insert the instrument in one direction, Le. generally flat or so thatface 258 of paddle area 256 is generally parallel to the upper and lowersurfaces of the upper and lower surfaces of the vertebral bodies betweenwhich it is being inserted. Once inserted, a surgeon may rotate handle252 in turn causing paddle area 256 to rotate within the vertebralspace. As sides 260 and 262 contact the upper and lower surfaces of thevertebral bodies, the disc space is distracted and the muscles andligaments are loosened. This helps prepare the disc space for insertionof the trial.

As one of skill in the art would understand, the size and shape of thepaddle distractor may vary and various sized instruments may be providedto accommodate different areas of the spine or distraction preferencesby the surgeon. Furthermore, distractors of various sizes may be used towithin the same space to distract the space in a step wise fashion. Asseen in FIG. 86 handle 252 may be releasably attached to shaft 254. Inthis fashion, a single handle may be provided with a set of paddledistractors with various sizes of paddle heads such that a surgeon mayselect different paddle distractors according to surgeon preferences andpatient anatomy. While any number of sizes may be used, in oneembodiment a set of paddle distractors with paddle heads having widthsof 10 mm to 17 mm, with a separate paddle distractor for each differentmillimeter width, is provided. In some embodiments, a set of paddledistractors are provided wherein there is a paddle distractor, with anappropriately sized paddle head, for each trial in the set or kit.

In an alternate embodiment, a dilator may be provided. With reference toFIG. 87, a dilator is shown. As seen in FIG. 87, dilator 264 is similarto paddle distractor 250 except that the end of dilator 264 isconfigured as a generally regular pyramid. As one of skill in the artwould understand, the shape and configuration of the dilator can aid thesurgeon in preparing the disc space by serving as a wedge as the dilatoris inserted into the intervertebral space. As further seen in FIG. 87,demarcations 266 along the generally pyramid area 268 correspond to thethickness or width of the area at that point. Thus, a dilator withwidths or thickness between 8 mm and 12 mm may be used and the surgeonmay distract the intervertebral space by a desired amount by insertingthe dilator to the appropriate depth. In an embodiment of the presentinvention, a set of dilators may be provided that correspond to a rangeof distraction sizes. For example, in one embodiment, a surgeon may beprovided with three dilators that contain a range of sizes of about 6-12mm, 8-14 mm, and 10-16 mm. As with the paddle distractor, handle 252 maybe releasably attachable such that a surgeon may use the same handle fordifferent dilators. As one of skill in the art would understand, a kitmay be provided that contains both dilators and paddle distractors. Inthis embodiment, a single handle may be used for both the differentdilators and different paddle distractors.

After preparing the intervertebral space the next step performedaccording to one embodiment, a surgeon determines the appropriate sizeof the assembly to use in the procedure as well as the desired positionof the assembly. The present invention contemplates tools and assembliesof various sizes to help a surgeon determine the appropriate prostheticdisc to implant. Trials, of various sizes, are commonly used in thistype of surgery to “test fit” items inserted into intervertebral spaces.Specially configured trials may be provided to aid in the positioning ofa second assembly based on the position of a first assembly.

As seen in FIG. 88, a first trial 300 is shown. In FIG. 88, only lowervertebral body 301 is shown. Also, in the following figures, the variousinstruments and assemblies are shown offset from the vertebral body.This view is provided to show more of the various tools and assembliesand one of skill in the art would understand that in practice, theassemblies and tools would lie within the intervertebral space. As oneof skill in the art would also understand, an upper vertebral body isalso present but, for the sake of visual clarity, not shown. Inoperation, first trial 300 may be inserted into the intervertebral space303 and the surgeon may then orient the trial 300 to determine the bestposition for the implant.

As discussed previously, a number of different trials of varying sizesmay be provided. The surgeon may test different trials to determine thesize, angle, and length of the implant appropriate for the patient. Thesurgeon may select the appropriate size trial based on a number ofcriteria including restoring disc height to the appropriate level orimplanting assemblies based on the structural characteristics of theupper and lower vertebral bodies, including for example, surface areaand strength of the surfaces.

As seen in FIG. 88, trial 300 comprises a first portion 305 thatincludes a trial head member 307 and a trial shaft member 309 and asecond portion 311 having a shaft member 313 and a handle member 315.Trial head member 307 is configured to mimic the size and shape of aprosthetic disc assembly. Trial head member 307 is further configuredwith keyed recesses 317, 319. Keyed recesses 317, 319, as discussed inmore detail below, are configured to receive and help guide chiselblades.

Trial shaft member 309 of first portion 305 of trial 300 extends alongan axis. Trial shaft member 309 of first portion 305 is connected totrial head member 307. As seen in FIG. 88, in one embodiment, trialshaft member 309 is connected at a position offset from the centerlineof trial head 307 in the direction away from the spinal cord (notshown). As one of skill in the art would understand, the offsetconnection imparts increased functionality to trial 300. The offsetconnection decreases the amount of distraction of the spinal cord toaccess the intervertebral space. The offset further reduces the riskthat the trial might contact the spinal cord, thus reducing the chanceof injury to the nervous system of the patient.

Trial head member 307 is further configured with a flat face 321 on theproximal side of trial head 307. Flat face 321 is configured as a stopwhen trial 300 is used with a chisel, which is described in more detailbelow. As seen in FIG. 88, trial shaft member 309 of first portion 305may also be shaped to accommodate the spinal cord. Area 323 of trialshaft member 309 of first portion 305 is carved out on the side facingthe spinal cord to further reduce the potential contact between trialshaft member 309 and the spinal cord. This area may be carved out from aportion of the shaft such that there is a reduced thickness of the shaftin the area of the spinal cord. The shaft 309, as seen in FIG. 88, hasother areas that are thicker to maintain rigidity and add strength tothe tool. As one of skill in the art would understand, variations couldbe employed to achieve similar results.

At the proximal end, trial shaft member 309 of first portion 305connects to second portion 311 of trial 300. Second portion 311 of trial300 also includes a handle member 315, which is connected to shaftmember 313 of second portion 311. As seen in FIG. 88, trial shaft member309 and shaft member 313 can be connected to each other. In oneembodiment, handle member 315 may include a mechanism by which it may beoperatively attached and removed from first portion 305. In onevariation, the mechanism is a lever 325 that may be actuated by a user.Shaft member 313 of second portion 311 is configured with a hollow areato receive the proximal end of trial shaft member 309 of first portion305. Trial shaft member 309 of first portion 305 may also be configuredto engage lever 325 (hidden). One of skill in the art would understandthat any number of different connection types including but not limitedto threaded connections, pins and slots, friction fits, or others may beused to connect trial shaft member 309 of first portion 305 with shaftmember 313 of second portion 311.

As further seen in FIG. 88, handle portion 315 is configured for a userto grasp. Handle 315 is designed to provide a surgeon with control overthe insertion and positioning of trial 300 within the intervertebralspace. In one embodiment, handle 315 may also be configured with a flatface 327. Flat face 327 of handle 315 is designed to give a surgeon animpaction surface. Surgeons or other users may strike the impactionsurface with a hammer or other tool to drive or insert the trial intothe intervertebral space, if desired.

As further seen in FIG. 88, trial 307 is configured with through holes318 and 320. Through holes 318 and 320 may be used by the surgeon toposition the trial within the intervertebral space. As one of skill inthe art would understand, a surgeon may take radiological or otherimages of the trial position during surgery. Through holes 318 and 320provide the surgeon with a reference point. For example, in oneembodiment, through hole 318 is placed at the center of the trial head.Thus, during implantation, the surgeon may use through hole 318 toposition the center of the trial. This may be useful to a surgeon toallow him or her to determine the point at which the assemblies of theprosthetic disc will be implanted, and hence the location(s) of theinstantaneous axis of rotations. Similarly, through hole 319 may be usedto measure whether the trial head is sufficiently within theintervertebral space. For example, by taking a lateral image of theintervertebral space, the surgeon can determine whether the trial hasbeen placed at a sufficient depth such that the assemblies will be fullywithin the intervertebral space when implanted.

In one embodiment, the trial has been positioned according to thepreferences of a surgeon, second portion 311 may be detached. Referringto FIG. 89, first portion 305 of trial 300 is shown after second portion311 of trial 300 has been detached. Referring to FIG. 89, the proximalend of shaft 309 may be configured with an engagement area 329.Engagement area 329 interacts with lever 325 of second portion 311 oftrial 300 (not shown).

Referring to FIG. 89, trial shaft member 309 of first portion 305 oftrial 300 may be configured with a particular shape. In an exemplaryembodiment, shaft 309 is configured with a generally rectangular shape.The shape of shaft 309 is designed to cooperate with other tools andparts used in the method. Accordingly, the hollowed out area of thesecond portion 311, and more particularly shaft 313, may be configuredto match the generally rectangular shape of shaft 309. Thus as should bereadily apparent, the shaft 313 may only be inserted over shaft 309 intwo orientations. This provides the tools with orientation preferences,which when applied to other parts of the method prove useful. As one ofskill in the art would understand, the particular shape may be changedand may include no limitations on the orientation of the various pieces(such as in circular shapes) or only one orientation allowed (such as ascalene triangle shape).

In one embodiment, a laminectomy centering guide is provided. Referringto FIG. 90, lamenectomy centering guide 312 comprises a template piece314. Template piece 314 is sized and dimensioned to approximate theneeded window or space that needs to be created in the lamina. Templatepiece 314 may be keyed to trial shaft portion 309, as seen in FIG. 90.Template piece may also be connected to a handle 316 so a surgeon mayposition the template piece 314 over the lamina to use said templatepiece 314 as a guide and then excise the required tissue/bone asdesired. In an embodiment of the present invention, the handle is angledwith respect to the front face of the laminectomy centering guide toprovide the surgeon with a better line of sight. In an embodiment of thepresent invention, the handle is angled by 10.degree. In an embodimentof the present invention, the handle is angled by between about3.degree. and 20.degree. A kit may be provided wherein there is morethan one laminectomy centering guide. In such an embodiment, varioussizes of a guide are provided. Accordingly, a kit may contain a guidefor each of the differently sized implants. In some embodiments, thehandle may be detachable from the template guide. In this fashion,various templates may be provided and only one handle is needed. As oneof skill in the art would understand, the precise configuration of thetemplate piece and handle may vary, and the methods of the presentinvention contemplate providing template pieces of varying sizes toaccommodate different patient requirements or surgeon preferences.

In one variation of an embodiment of a method according to theinvention, after detaching second portion 311 of trial 300, paths may becut in the upper and lower surfaces of the vertebral bodies within theintervertebral space. The paths cut into the surfaces of theintervertebral space are generally configured and dimensioned tocorrespond to accommodate the keels on the endplates of the prostheticdisc assemblies. Accordingly, the paths cut, their size, their angle,etc. each relate to the specific type of keel (and their configurations)used in the prosthetic disc being inserted.

Referring to FIGS. 89 and 91, trial head 307 of trial 300 is configuredto aid in the alignment and guidance of the chisel. In FIG. 91, chisel329 is shown after insertion onto first portion 305 of trial 300. Chisel329 has a blade portion 331, a shaft portion 333, and a handle portion335. Blade portion 331 is forked having two blades 337 and 339 connectedto a central member 341. Blade portion 331 is configured and dimensionedsuch that upon insertion, blades 337, 339 partially extend above andbelow trial head 307. As best seen in FIG. 91, trial head 307 isconfigured with two recesses 317 and 319, which are keyed into the upperand lower surfaces of trial 307. Blades 337 and 339 partially ridewithin keyed recesses 317 and 319 as the chisel blades are driven intothe vertebral bodies to create or clear a path in the bone. As one ofskill in the art would understand, trial head 307 is configured toreceive and guide blades 337 and 339 of chisel 329, however, alternatechisels and blade designs may be employed to achieve similar results.

Referring to FIG. 91, chisel portion 331 is connected to shaft portion333. As described above, in one embodiment, the chisel portion 331 maybe offset from the shaft portion 333 of chisel 329. This design featuremaintains the offset configuration discussed with respect to the trialto maintain the path-cutting tool away from the spinal cord.

Shaft portion 333 of chisel 329 is configured with a hollow section sothat it may fit over and slidingly engage shaft 309 of trial tool 300.Similar to shaft 309 of the trial tool 300, shaft 333 of the chisel tool329 may be cut away on the side facing the spinal cord, as seen in FIG.91. This feature (as the similar feature does in the trial tool) createsadditional space on the side of the spinal cord to minimize potentialcontact or injury with the spinal cord. In one embodiment, the hollowsection of shaft portion 333 of chisel 329 is shaped to match the shapeof shaft 309 of trial tool 300. As discussed previously, this featurerequires insertion of chisel 329 over trial 300 at a particularorientation that ensures that the blades will be positioned correctly,i.e. with the blades cutting a pathway into the upper and lower surfaceof the vertebral bodies. As one of skill in the art would understand, atwo-orientation configuration is adequate where the upper and lowerkeels of the prosthetic disc are similar, equivalent, or the same. Wherethe keels of the prosthetic disc assembly have different keels (andhence the paths that need to be cut need to be different), a singleorientation device may be desired.

Handle portion 335 is connected to shaft portion 333 of chisel 329. Inone embodiment, handle portion 335 contains a shaft member 343 connectedto an impact member 345. Shaft member 343 is hollow and shaped toreceive shaft 309 of trial 300. In one variation, impact member 345 iscylindrical in shape and has a flat face 347, which serves as an impactarea. Flat face 347 may have a through hole 349. As chisel 329 is driveninto position (guided by trial 300), central member 341 will contacttrial head 307 at the final insertion point, i.e. the insertion pointdetermined by the trial. Similarly, the length of shaft 309 and chisel329 are configured such that when chisel 329 reaches its final insertionpoint, the end of shaft 309 is flush with the flat face 347 of handleportion 345. Accordingly, the end of shaft 309 fits through bore hole347 and, if chisel 329 is driven by impacting flat face 347 includingbore hole 349, the impaction tool will stop driving chisel 329 intobone. This combination of features provides a guide for the surgeon toindicate when the appropriate path has been cut into the vertebralbodies as well as acting as a stop to safeguard against creating longerpathways than required by the keels of the prosthetic disc assemblies.

According to one embodiment of a method of the present invention, oncethe appropriate paths have been cut, handle portion 335 of chisel 329may be removed. Referring to FIGS. 91 and 92, handle portion 335 hasbeen removed from shaft portion 333 of chisel 329. As seen in FIG. 92,handle portion 335 and shaft portion 333 of chisel 329 are engaged withrespect to each other at area 351. As handle portion 335 slides overshaft 309 of trial 300, handle portion 335 engages shaft 333 of chisel329. As best seen in FIG. 92, handle portion 335 is configured tointerface with shaft 333 of chisel 329. One of ordinary skill in the artwould understand that any variety of configurations, including tongueand groove, threaded connections, or other configurations could beemployed to achieve similar results.

According to one embodiment of a method of the present invention, afterremoving the handle portion 335 of chisel 329, an outrigger orpositioning member may be slid onto trial shaft 309. As seen in FIG. 93,positioning member 353 slides onto shaft 309 until it engages with shaftportion 333 of chisel 329 at engagement area 351. Positioning member 353is configured with a hollow section that is shaped to match the shape ofshaft 309 of trial 300. In this embodiment, due to the rectangularconfiguration, the positioning member 353 is placed in a particularorientation, which will not move radially with respect to shaft 309 oftrial 300.

In one embodiment, shaft 333 and blade portion 331 may remain inserted.Such a feature may provide a stop against which positioning member 353may contact (at area 351) and may serve to lock trial 300 in place as aresult of a friction fit between blades 337 and 339 and the vertebralbodies with which they may contact. Such a feature may secure theposition of trial 300 and make it less likely that trial 300 will moveduring the remaining steps.

In one embodiment, positioning member 353 comprises an attaching portion355, i.e. the portion that slides over shaft 309 of trial 300, and aguiding portion 357. Guide portion 357 is attached or connected toattaching portion 355 by a linking member 359 as seen in FIG. 93. Guideportion 357 serves as a hitch or post onto which a second chisel toolmay be placed. While guide portion 357 is shown as generallycylindrical, any number of different shapes and configurations could beused. For example, guide portion could be generally rectangular,pyramidal, or square. The invention contemplates a guide portion shapedand configured to mate or key with the shape and configuration of theelongated shaft. Accordingly, one of skill in the art would understandthat guide portion 357 is shaped to act as a guide and direct a chiseltool along a path parallel to trial 300.

With reference to FIG. 94, second chisel tool 361 is shown. Secondchisel tool 361 has a chisel portion 363, shaft portion 365, and handleportion 367. As seen in FIG. 91, chisel portion 363 of second chisel 361is configured similar to first chisel portion 331 of first chisel 329,except that the chisel portion 363 of second chisel 361 is not forked asit is in first chisel 329. In this regard, chisel portion 363 of secondchisel 361 does not accommodate a trial head and accordingly is designedor constructed from one piece. The upper and lower surfaces 369, 371 ofchisel portion 363, however, have blade portions or sharp edgesconfigured similar to blades 337, 339 of chisel portion 331 of firstchisel 329.

A shaft portion 365 is attached to the second chisel portion 363 ofsecond chisel 361. Second chisel portion 363 may be similarly offsetfrom shaft portion 365 as in previous descriptions to accommodate thespinal cord. Shaft portion 365 extends from chisel portion 363 and maycomprise a sleeve or hollow body. As one of skill in the art wouldunderstand, the interior walls of shaft portion 365 may be shaped tomatch the external shape of guiding portion 357. In one embodiment, anopening may be formed along shaft portion 365 to provide access to theinterior of shaft portion 365. Said opening is sized to accommodateguiding portion 357. Accordingly, second chisel 361 may be placed ontoguiding portion 357 and slid towards the vertebral bodies. As guidingmember 357 rides within the hollow body, which is shaped to match thehollow body of shaft portion 365 of second chisel 361, the second chiselis directed along a path which is parallel to trial 300 and spaced aparta set distance from trial 300.

In alternate embodiments, guiding portions and attaching members may beintegral to the second chisel, and thus slidably engage or attach withthe shaft of the first chisel. In alternate embodiments, a centralmember may be used that selectively engages the shafts of both thetrial, first chisel, or second chisel. Accordingly, as one of skill inthe art would understand, the precise mechanism by which the pathwaysare created may be any number of means.

According to one embodiment of a method of the present invention and asseen in FIG. 95, the second chisel 361 may be driven into position bythe surgeon. Shaft portion 365 is attached to handle portion 367. Asurgeon may grip handle portion 367 and use it to position second chisel361. In one embodiment, handle portion 367, as seen in FIG. 95, is acylindrical body attached to shaft portion 365. Handle portion 367 mayhave a plurality of bore holes to decrease the weight of the overalltool. Handle portion includes a flat face 369, which serves as animpaction surface. Accordingly, a surgeon may use an impact tool todrive the second chisel 361. In alternate embodiments, shaft portion 309is configured with a length that abuts underside face 370 of handleportion 367 when chisel 361 is in its final position. In theseembodiments, flat face 370 may act as a stop. At this point in themethod, four pathways have been made, two pathways in the upper andlower vertebral bodies each of the disc area being treated.

In an embodiment of the method presented herein, after cutting bothpaths into the vertebral bodies, a surgeon may remove only the secondchisel 361. With reference to FIG. 96, a surgeon would remove the secondchisel 361 and outrigger 353 from first trial 305, thus leaving firsttrial 305 in place. First trial 305 and first chisel 329 are left inplace to both keep the intervertebral space separated as well as allowshaft 309 of trial 305 to serve as a guide for assembly implantation.

As seen in FIG. 96, an implant holder 390 attached to one assembly 383is shown. Implant holder 390 is releasably attached to assembly 383.Implant holder 390 also comprises an implant guide 392. Implant guide392 is rigidly attached to said implant holder and comprises a matingportion 394 that is configured to mate with shaft portion 309 of firsttrial 305. In an embodiment, mating portion 394 is configured as anelongated rectangle with a groove sized to accommodate the shape andconfiguration of shaft portion 309 of first trial 305. As one of skillin the art would understand, mating portion 394 attached to implantholder 390 keys implant holder 390 to shaft portion 309. Accordingly, asurgeon may place assembly 383 in an approximate position by introducingkeels 396 and 398 into paths 371 (not shown) and 377. The surgeon maythen swing implant holder 390 and key mating portion 394 onto shaftportion 309 of first trial 305. At that point, a surgeon may then driveassembly 383 into position. As one of skill in the art would understand,mating portion helps guide assembly 383 into position by maintaining aproper spacing between implant holder 390 and first trial 305.Additionally, mating portion 394 ensures that the assembly is insertedparallel to first chisel 305. With reference to FIG. 97, implant holder390 is shown with assembly 383 60 inserted. As seen in FIG. 97, matingportion 394 is configured to provide a keyed mating connection beforeassembly 383 is inserted as well as allow implant holder 392 to driveassembly 383 along a path parallel to first trial 305 until assembly 383has been inserted to a proper depth.

With reference to FIG. 98, implant holder 390 is comprised of a shaftportion 396 and handle portion 398. As seen in FIG. 98, handle portion398 may be detached from shaft portion 396. The attachment mechanism maybe any number of means although in this embodiment, handle portioncontains an internally threaded rotatable cylinder 400 attached tohandle portion 398 of implant holder 390. Internally threaded rotatablerod 400 is configured to mate with one end of shaft portion 396, whichcomprises an externally threaded cylindrical portion 402. Accordingly,rotation of internally threaded cylinder 400 can thus serve to eitherattach or release handle portion 398 from shaft portion 396 of implantholder 392.

In an embodiment of the present invention, releasing handle 398 fromimplant holder 392 exposes a proximal end 404 of shaft 396 of implantholder 390. With reference to FIG. 99, shaft 396 of implant holder 390may be releasably attached to prosthetic disc assembly 383. To releaseshaft 396 from assembly 383, a surgeon may use a driver 406 as seen inFIG. 99. Driver 406 may be configured with a head 408. Shaft 396 has afirst internal rod or elongated screw 410 comprising a threaded end(hidden) and a shaped receiving end 412. As one of skill in the artwould understand, head 408 of driver 406 is shaped to mate withreceiving end 412 of first internal rod 410 and driver 406 may rotatefirst internal rod 410, which in turn rotates the threaded end of saidrod. Threaded end of rod 410 engages assembly 383, and moreparticularly, an internally threaded bore hole in a stabilizing member414 attached to assembly 383. Threaded end of shaft 410 provides theattachment and release mechanism of the implant holder to assembly 383.As one of skill in the art would understand, the attachment can be byany number of different mechanisms. Accordingly, as seen in FIG. 100,shaft 396 is seen released from assembly 383 after assembly 383 has beeninserted into the intervertebral space.

In an embodiment of the present invention, assembly 383 has astabilizing member 414 attached to assembly 383. With reference to FIG.101, stabilizing member 414 is shown attached to assembly 383.Stabilizing member 414 is configured to prevent the articulatingsurfaces of assembly 383 from moving. Stabilizing member 414 is attachedto assembly 383 but may disengage or release from the assembly by thesurgeon as described in more detail below. Accordingly, duringimplantation of a two assembly artificial prosthetic disc design,stabilizing member 414 locks the articulating surfaces of assembly 383until stabilizing member is released.

With reference to FIG. 102, after insertion of assembly 383, first trial305 is removed from the intervertebral space. Second assembly 381 isthen inserted using an implant holder as described above and as seenpreviously except that no guiding member is used in this step. Inalternative embodiments, a guiding member may be used if a shaft orother elongated structure is connected to assembly 383. With referenceto FIG. 103, handle 398 of implant holder 390 may be separated fromshaft portion 396. With reference to FIG. 104, driver 406 may be used torelease shaft 396 of implant holder 390 from assembly 381. As seen inboth FIGS. 103 and 104, second assembly 381 has a stabilizing memberattached. In alternative embodiments, only assembly 383 may have astabilizing member as stabilizing member 414 attached to first assembly383 may be sufficient to maintain stability and the need forimmobilization of the articulating surfaces of the assemblies may nolonger be needed once both assemblies have been implanted. As seen inFIG. 104, shaft 396 has a second internal rod or elongated screw 411comprising a threaded end (hidden) and a shaped receiving end 413. Asone of skill in the art would understand, head 408 of driver 406 isshaped to mate with receiving end 413 of second internal rod 411 anddriver 406 may rotate first internal rod 411, which in turn rotates thethreaded end of said rod. Threaded end of rod 411 engages a screw instabilizing member 414, which in turn connects stabilizing member 414 toassembly 381. Threaded end of shaft 411 provides the attachment andrelease mechanism of the implant holder and stabilizing member 414 toassembly 381. As one of skill in the art would understand, theattachment can be by any number of different mechanisms.

With reference to FIG. 105, shaft 396 may have a third internal rod orelongated screw 415 comprising a threaded end (hidden) and a shapedreceiving end 417. As one of skill in the art would understand, head 408of driver 406 is shaped to mate with receiving end 417 of third internalrod 415 and driver 406 may rotate third internal rod 415, which in turnrotates the threaded end of said rod. Threaded end of rod 415 engages ascrew in stabilizing member 414, which in turn connects stabilizingmember 414 to assembly 381. Threaded end of shaft 415 provides theattachment and release mechanism of the implant holder and stabilizingmember 414 to assembly 381. As one of skill in the art would understand,the attachment can be by any number of different mechanisms.

With reference to FIG. 106, assembly 381 is shown implanted into theintervertabral space after shaft 396 of implant holder 390 andstabilizing member 414 has been released. As seen in FIG. 106, threadedbore holes 420 and 422 are configured to interact with screws 424 and426 (hidden) of stabilizing member 414, said screws having been rotatedby the action of driver 408 on rods 411 and 413 of shaft 396. As furtherseen in FIG. 106, disc assembly 383 still contains stabilizing member414 attached to assembly 383.

With reference to FIG. 107, stabilizing member 414 of assembly 383 maybe released after implantation of assembly 381. As seen in FIG. 107,shaft 396 of implant holder 390 may be reattached to stabilizing memberas described above. With reference to FIGS. 108 and 109, driver 406 maythen be used to engage mated receiving ends of rotatable internal shafts411, 413. The opposite ends of rotatable internal shafts (not shown) areconfigured to engage screws (hidden) in stabilizing member 414, saidscrews connecting stabilizing member 414 to assembly 383. Accordingly,driver 406 may be used to rotate internal rods 411, 413, which actuatescrews in stabilizing member 414 to either attach or release stabilizingmember 414 from assembly 383.

In an embodiment of the present invention, shaft 396 may be connected tostabilizing member 414 through one rod prior to the disengagement ofstabilizing member 414 from assembly 396. Accordingly, in an embodimentimplant holder connects to stabilizing member via a threaded rotatablerod and stabilizing member connects to an assembly of the prostheticdisc via a screw. In an alternate embodiment, the stabilizing member isconnected to the implant holder by more than one rotatable shaft. In analternate embodiment, the stabilizing member is connected to an assemblyof the prosthetic disc by more than one screw. Where the stabilizingmember is connected to an assembly by only one screw, locking of theassembly may be accomplished by physical interference of the stabilizingmember with the endplates or other structure of the assembly tophysically limit rotation of the assembly. Where the stabilizing memberis connected to the assembly by more than two screws, the rigidity ofthe stabilizing member locks the assembly in place. As stabilizingmember is used to lock or prevent articulation of the first assemblyimplanted into the intervertebral space, any number of mechanisms may beused to prevent said articulation or movement. Accordingly one of skillin the art that screws, interference fits, prongs, tabs, or otherconfigurations can be used on the stabilizing member to preventarticulation of the assembly. With reference to FIG. 110, assemblies 381and 383 are shown in their final position (offset).

With reference to FIG. 111, a cross section of shaft 396 of implantholder 390 is shown. As seen in FIG. 111, in this embodiment, there arethree elongated rods 430, 432, and 434 that act to either connectstabilizing member to shaft 396 or stabilizing member to an assembly. Asrevealed by the cross section view of shaft 396, the elongated rods maybe configured to allow longitudinal movement within the shaft. Thismovement allows the shafts to individually engage either the threadedbore or screws of the stabilizing member and further allows for properthreading or mating between the end of an elongated shaft and its matingportion. Elongated shafts 430, 432, and 434 may be retained within theshaft and provided a limited range of movement by using retaining clip436. As one of skill in the art would understand, elongated shafts 430,432, and 434 may be formed with a portion having a smaller diameter thanthe rest of the shafts. Clip 436 may then be formed with two arms 438and 440, which may contact or abut inner walls of the elongated rod butotherwise not contact or interfere with the elongated rod. In thismanner, depending on the length of the portions of the rod having asmaller diameter, the elongated rods may translate within the shaft. Thelength of translation may vary but in an embodiment of the presentinvention, the elongated rods may translate between about 1 mm and 4 mm.

As described above, methods and tools are provided that allow a surgeonto implant a prosthetic disc from the posterior approach. The methodsallow a surgeon to implant more than one assembly, which may havearticulating surfaces. In general, the methods provide a means by whichthe surgeon can properly align each prosthetic disc with respect to eachother. In operation, the methods also generally minimize distraction andinjury to the spinal cord.

In an alternative embodiment, after cutting both pathways or grooves,the second chisel, first chisel, attaching member, and trial may beremoved. Referring to FIG. 112, the intervertebral disc space is shownafter it has been prepared by the methods and tools of an embodiment ofthe present invention. As seen in FIG. 112, four separate pathways 371,373, 375, 377 have been cut into the surfaces of the vertebral bodies.As one of skill in the art would understand, the paths cut by themethods and tools of the present invention provide spaces for theinsertion of keels spaced apart by a predetermined distance. Moreover,each pathway is generally cut parallel to each other. The upper andlower paths are aligned within the same plane. As one of skill in theart would understand, the present methods and tools provide a surgeonwith the ability to insert multiple assemblies into the intervertebralspace from a posterior approach.

According to one embodiment of a method of the present invention, afterremoving the chisels and trial, an assembly may be inserted into theintervertebral space. Referring to FIG. 113, a disc holder 379 is shownattached to a prosthetic disc assembly 381 according to the presentinvention. Preferably, disc holder 379 maintains assembly 381 in aneutral position. Disc holder 379 may be of any variety of designs andthe methods of the present invention are not limited to any particulardisc holders. As one of skill in the art would understand, disc holderis used to insert assembly 381 into the intervertebral space. In oneembodiment, a first prosthetic disc 381 has an upper and lower keel thatrides within the paths cut by the first chisel.

Once the first disc assembly is inserted, the disc holder may releasethe first prosthetic disc. As seen in FIG. 114, the disc holder hasreleased assembly 381 and assembly 381 is shown in its final orimplanted position in the intervertebral space. Referring to FIG. 115,the upper vertebral body is not shown for sake of clarity. Next, thesecond assembly may be inserted. As seen in FIG. 115, a second assembly383 is inserted into the intervertebral space. The upper and lower keelsof the second assembly ride within the paths cut by the second chisel.Once inserted, the disc holder releases the second assembly (FIG. 116).FIGS. 117 and 118 show the two assemblies inserted into the disc space.The prosthetic disc assemblies are shown in their neutral position. Asone of skill in the art would understand, after implantation the spacingbetween the assemblies is such that the endplates of the assemblies canarticulate as if they were a single articulating surface.

Now, turning to FIG. 119, another embodiment of a posterior discassembly is illustrated. In this particular embodiment a posteriorspinal disc 400 which contains multiple elements according to thepresent invention is shown. FIG. 120 illustrates an exploded view of thedisc assembly 400, which more clearly shows the individual elements ofthe spinal disc 400. FIG. 120 illustrates an upper endplate 402, a lowerendplate 404, a flexible core element 406 and a slider plate 408. Theendplates 402, 404, flexible core element 406, and the slider plate 408may be composed of a variety of biocompatible materials, includingmetals, ceramic materials and polymers. Such materials include, but arenot limited to, aluminum, alloys, and polyethylene. The outer surfacesof the endplates 402, 404 may also contain a plurality of teeth whichmay be maybe coated with osteoconductive material, antibiotics or othermedicament, or may have a porous or macrotexture surface to help rigidlyattach the endplates 402, 404 to the vertebral bodies by promoting theformation of new bony ingrowth. Each of these elements and theinterconnections between the associated elements will be discussed ingreater detail with reference to FIGS. 121-126.

In the present embodiment, the upper endplate 402 is configured with aplurality of keels 414 that engage with an intervertebral body and anextension portion 403 which is configured to be in contact with theslider plate 408. The extension portion 403 is configured with acurvature which corresponds with a curvature associated with the sliderplate 408. The extension portion 403 and the plate 408 being incommunications allows rotational and translational motion to occur. Asmentioned previously, the present disc assembly can mimic or partiallymimic the varying IAR and COR to the extent desired by a physician whilealso preserving the stability of the device.

Although the present embodiment utilizes a keel 414 so that it may beused to guide the disc assembly into position during insertion into thetreated area of the spine, ridges, teeth or any other type of mechanismto attach the endplate 402, 404 to the vertebral body may also be used.Also, as mentioned previously, the use of one or more keels 414 may alsoincrease bone to implant surface contact, thereby decreasing thelikelihood that the assembly will shift or move out of position.

The extension portion 403 of the upper endplate 402 is spaced apart fromthe base of the upper endplate 402 and fits into a cavity 418 in anupper portion of the flexible core element 406. The extension portion403, in the present embodiment, is provided with a flat surface having alength of 17 mm, a width of 7 mm and a height of 2.5 mm. However, inother embodiments the contact surface of the extension portion 403 maybe configured with a curvature or dimensioned for optimizing the contactsurface. Although in the present embodiment, the extension portion 403of the upper endplate 402 is configured with a flat surface, anygeometry may be used that adapts within the flexible core element 406and communicates with the slider plate 408. The lower endplate 404 isalso configured with multiple keels 414 to engage with an adjacentvertebral body. The lower endplate 404 is also configured with anextension portion 416 which is adapted to fit within a cavity in a lowerportion of the flexible core element 406. The extension portion 416 isspaced apart from the base of the lower endplate 404 and is configuredto conform to the cavity formed in the lower portion of the flexiblecore element 406. In this embodiment, the extension portion 416 isconfigured as an elongated and curved plate having a length of 17 mm, awidth of 7 mm and a height of 1.5 mm. It should be noted that theextension portion 416 may be configured to be in any geometry to conformand fit within the cavity formed within the lower portion of theflexible core element 406. The upper endplate 402 and the lower endplate404 are also provided with screw holes 412, 414 for receiving aninstrument for positioning the disc 400 within the intervertebral space.

The flexible core element 406 is composed of a flexible material thatmay be tensioned, compressed or be a combination of tensioned andcompressed elements. The flexible core element 406 may be made ofresilient material that provides suitable resistance to stretching orcompression. The compression element helps support axial loading alongthe treated vertebral bodies so their relative positions approximate ahealthy vertebral body supported by a natural disc. The flexible coreelement 406 also helps in controlling the bending or movement of thevertebral bodies relative to each other. The flexible core element 406is configured and adapted to allow for compression and translation byproviding a cavity in the upper portion and a cavity in the lowerportion which receives the extension portions of the upper 402 and lowerendplates 404. The flexible core element 406 is composed of a resilientmaterial to allow for rotation to occur.

The flexible material in one particular embodiment is composed ofPolycarbonate Urethane. However, any flexible material that isbio-mechanical and biologically compatible may be used. As mentionedabove, the core element 406 has an upper portion and a lower portion.The upper portion is configured to receive and retain the slider plate408 within the cavity 418. The lower portion is configured to receiveand retain the extension portion 416 of the lower endplate 404 withinthe cavity 420.

The slider plate 408 is a metal plate having an upper and lower surface.The upper surface of the slider plate 408 is generally a flat surfacehowever a curvature that corresponds to the curvature of the extensionportion 403 of the upper endplate 402 may also be utilized.Additionally, the slider plate may be configured to be of any geometricshape which is capable of communicating with an extension portion of theupper endplate. In the preferred embodiment the slider plate 408 iscomposed of metal, however the slider plate 408 may be comprised of anyelement that allows a friction coefficient that enables the extensionportion 403 translate or axially rotate relative to the slider plate408.

FIG. 121 illustrates a cross sectional view of one particular embodimentof the disc assembly 400. In this embodiment of the disc assembly 400,the upper endplate 402 is in communication with the slider plate 408through the extension portion 403. The extension portion 403 is adaptedinto the flexible core member 406. The extension portion 403 is slightlysmaller than the space provided between one end of the flexible coreelement 406 to the other end. As a result, the extension portion 403 maytranslate from 0.5 mm to 1 mm along the slider plate 408. Additionally,the upper endplate 402 may translate and axially rotate relative to theflexible core element 406. Thus, the upper endplate 402 can translate inone direction or in a second direction by configuring the extensionportion 403 to communicate with the slider plate 408.

The lower endplate 404 is also provided with an extension portion 416that is fitted into the flexible core element 406. In this particularembodiment, the lower endplate 404 is adapted to fit tightly within theflexible core element 406 to limit the translational and axial motion ofthe lower endplate 404 with respect to the flexible core element 406.However, the lower endplate 404 is adapted to extend and flex within theflexible core element 406, as the flexible core element 406 iscompressed or stretched. In this embodiment, the length, height, andwidth of the cavity in the lower portion of the flexible core element406 is substantially equal to the length, height, and width of theextension portion 416 of the lower endplate 404, thereby limitingtranslational and rotational motion. As explained above, the lowerendplate 404 is configured to compress and flex on the flexible coreelement 406, providing flexion and extension. The upper and lowerendplates 402 and 404 are also provided with screw holes 410, 412 forreceiving an instrument which is utilized to position the disc assemblywithin the intervertebral space of the spine. The upper and lowerendplates 402 and 404 are also configured with a base portion that havea spherical contact surface which increases the surface area forcontacting with the adjacent vertebral body.

FIG. 122 illustrates a cross-sectional view of another embodiment of adisc assembly 420 according to the present invention. In this particularembodiment, the disc assembly 420 is comprised of an upper endplate 422,a lower endplate 424, a flexible core element 426 and a slider plate428. The extension portion 430 of the upper endplate 422 is adapted tofit within a cavity in an upper portion of the flexible core element426. The extension portion 430 of the lower endplate 424 is adapted tofit within a cavity in the lower portion of the flexible core element426. The flat surface of the extension portion 434 of the lower endplate424 is configured with a curvature for enabling flexion and extensionwith respect to the flexible core element 426. As illustrated in FIG.122, the cavity 438 in lower portion of the flexible core element 426 islarger than the extension portion 434 of the lower endplate 424, whichallows greater amount of flexion and extension to occur when theflexible core element 426 is either compressed or stretched.

The slider plate 428 allows for axial rotation and translation(anterior/posterior sliding motion) within the device. Flexion,extension and lateral bending motions are a hybrid combination ofmovement available due to the spherical feature provided on the insideof the endplate 422 that mates to the flexible core element 426. As inthe previous embodiments, the upper and lower endplates 422, 424 areprovided with multiple keels 432, 436 to attach the endplates 422, 424to adjacent vertebral bodies. The disc assembly 420 is also providedwith threaded holes 442, 444 on the posterior faces of the endplates422, 424 for receiving an instrument which is used to position the discassembly within the disc space of the spine. A locating groove thathelps to align the screw holes as well as resist twisting forces whilebeing inserted is also provided on the posterior portion of the discassembly.

FIG. 123 illustrates yet another embodiment of the invention. In thisembodiment, the disc assembly 450 is comprised of an upper endplate 452,a lower endplate 454, a flexible core element 456, a slider plate 458,and cord 460.

The upper endplate 452 and lower endplates 454 are configured with keels462, 464 which engage with the corresponding adjacent vertebral bodies.The upper and lower endplates 452, and 454 are also provided withthreaded screw holes 466, 468 on the posterior faces of the upper andlower endplates 452, 454 for receiving an instrument to position thedisc assembly within the spine.

The disc assembly 450 further includes the flexible core element 456which is situated between the upper and lower endplates 452, 454. Theinner portion of the flexible core element 456 is configured with acavity in the upper portion that receives and retains the slider plate458 and the extension portion 470 of the upper endplate 452. The lowerportion of the flexible core element 456 is also configured with acavity which receives and retains the extension portion 472 of the lowerendplate 454. The extension portion 470 of the upper endplate 452 isadapted to communicate with the slider plate 458 to allow fortranslation since the extension portion 470 is slightly smaller inlength than the slider plate 458. The extension portion of the upperendplate is configured to be slightly smaller than the slider plate 458and fits within a first cavity in the inner portion of flexible coremember, allowing for some space between the edges of the extensionportion and the edge of the inner portion. The upper endplate istranslated or rotated axially, the extension portion moves along theslider plate thereby providing translations and axial motion in thespinal segment. The amount of translation which occurs between theextension portion 470 and the slider plate 458 can be adapted bylengthening or shortening the extension portion 458.

The extension portion 472 of the lower endplate 454 is configured withas spherical surface and is positioned tightly within a second cavity inthe inner portion of the flexible core element 456. The configuration ofthe extension portion 472 provides flexion and extension motion when thelower endplate 454 is moved by the natural movements of the spine.

The disc assembly 450 is also provided with a central shaft in which acord 460 is utilized to attach the assembly 450 as a single structure.The cord 460 may be composed any elastic or flexible material that isbiocompatible. The cord 460 has a first end 476 and second end 478 thatconfigured to be slightly larger than the body of the cord 460. Thisconfiguration allows the cord 460 to be retained within the discassembly 450. However, any structural or mechanical configuration thatretains the cord 460 within the disc assembly may 450 be utilized. Forinstance, cord 460 may be attached to the endplates 452, 462 through aclip or a set screw.

The cord 460 may also be tensioned so that the assembly 450 is firmlyheld together. The tension of the cord 460 may vary depending on howmuch motion is required for the specific patient requiring the discassembly implant 450. The characteristics of the cord 460 may be changeddepending on what is required, for instance, the cord may be composed ofa solid flexible material or a be a hollow member. The cord 460 may alsobe positioned in various locations through the disc assembly. Forexample, a single cord may be placed on the perimeter of the discassembly or in position along the surface of the endplates. In anotherembodiment, the disc assembly may use a plurality of cords to attach theassembly as a single structure and to restrict the rotational motion ofthe disc assembly. When multiple cords are used, the cords may spacedapart in any location along the perimeter of the endplates to achievethe optimal results for either limiting or allowing motion in the discassembly as well as maintaining the structural integrity of the discassembly. In another embodiment, the core may be comprised of variousflexible elements having different flexibilities and/or durometers.

FIG. 124 illustrates two disc assemblies 480 and 482 according to thepresent invention. As described above, two posterior disc assemblies480, 482 may be inserted into the intervertebral space to provide anoptimal solution for disc replacement. The positioning of two discassemblies allows the motion of the spine to mimic the actual motion ofthe disc nucleus. FIG. 125 illustrates the two disc assemblies 480 and482 positioned in the intervertebral space between adjacent vertebralbodies 484 and 486. FIG. 126 illustrates a posterior view of the twodisc assemblies 480 and 482 positioned in the intervertebral space ofadjacent vertebral bodies 484 and 486.

The various features and embodiments of the invention described hereinmay be used interchangeably with other feature and embodiments. Finally,while it is apparent that the illustrative embodiments of the inventionherein disclosed fulfill the objectives stated above, it will beappreciated that numerous modifications and other embodiments may bedevised by one of ordinary skill in the art. Accordingly, it will beunderstood that the appended claims are intended to cover all suchmodifications and embodiments which come within the spirit and scope ofthe present invention.

What is claimed is:
 1. An intervertebral prosthetic disc comprising: afirst endplate having a plurality of protrusions for attaching to afirst adjacent vertebrae and an extension portion extending towards asecond adjacent vertebrae, the extension portion being spaced apart froma base of the first endplate when assembled; a second endplate having aplurality of protrusions for attaching to the second adjacent vertebraeand an extension portion extending towards the first adjacent vertebrae,the extension portion being spaced apart from a base of the secondendplate when assembled; a resilient member having an upper portion anda lower portion; a slider plate having an upper and lower surfacepositioned and enclosed within a first cavity in the upper portion ofthe resilient member, wherein the upper surface of the slider plate isconfigured to contact a lower surface of the extension portion of thefirst endplate; and, wherein the extension portion of the first endplateis adapted to fit within the first cavity in the upper portion of theresilient member and the extension portion of the second endplate isadapted to fit within a second cavity in the lower portion of theresilient member, wherein the extension portion of the first endplateengages with the upper surface of the slider plate to allow translationor rotation of the extension portion relative to the slider plate,wherein a length of extension portion of the first endplate is smallerthan a length of the slider plate.
 2. The implant of claim 1, whereinthe extension portion of the first endplate is configured to slide onthe upper surface of the slider plate.
 3. The implant of claim 1,wherein a surface of the extension portion of the first endplate incontact with the slider plate is substantially flat.
 4. The implant ofclaim 1, wherein a surface of the slider plate on which the extensionportion of the first endplate is in contact is substantially flat. 5.The implant of claim 1, wherein the extension portion of the firstendplate is capable of translating along the slider plate from 0.5 mm to1 mm.
 6. The intervertebral prosthetic disc of claim 1, wherein theextension portion of the first endplate is spaced apart from the base ofthe first endplate by a recessed annular channel separating the base ofthe first endplate from the extension portion of the first endplate. 7.The intervertebral prosthetic disc of claim 1, wherein the first cavityis larger than the second cavity.
 8. The intervertebral prosthetic discof claim 1, wherein the entire extension portion of the first endplateis fully contained within and enclosed by the first cavity and theentire extension portion of the second endplate is fully containedwithin and enclosed by the second cavity.
 9. The intervertebralprosthetic disc of claim 1, wherein the slider plate has a first lateralend and a second lateral end, and both of the first and second lateralends are positioned within the first cavity.
 10. The intervertebralprosthetic disc of claim 1, wherein the extension portion of the secondendplate is adapted to fit tightly in the second cavity to limit thetranslational and axial motion of the second endplate with respect tothe resilient member.
 11. The intervertebral prosthetic disc of claim 1,wherein the extension portion of the first endplate is a single integraland continuous piece extending from the first endplate and the extensionportion of the second endplate is a single integral and continuous pieceextending from the second endplate.
 12. The intervertebral prostheticdisc of claim 1, wherein the first endplate has a first keel forengaging the first adjacent vertebrae and the second endplate has asecond keel for engaging the second adjacent vertebrae.
 13. An implantcomprising: a first endplate having a plurality of protrusions forattaching to a first adjacent vertebrae and an extension portionextending towards a second adjacent vertebrae, the extension portionbeing spaced apart from a base of the first endplate when assembled; asecond endplate having a plurality of protrusions for attaching to thesecond adjacent vertebrae and an extension portion extending towards thefirst adjacent vertebrae, the extension portion being spaced apart froma base of the second endplate when assembled; a resilient member havingan upper portion and a lower portion; a slider plate having an upper andlower surface positioned and enclosed within a first cavity in the upperportion of the resilient member, wherein the upper surface of the sliderplate is configured to contact a lower surface of the extension portionof the first endplate; and, wherein the extension portion of the firstendplate is adapted to fit within the first cavity in the upper portionof the resilient member and the extension portion of the second endplateis adapted to fit within a second cavity in the lower portion of theresilient member, wherein the extension portion of the first endplateengages with the slider plate to allow translation of the first endplaterelative to the slider plate, wherein a length of the extension portionof the first endplate is smaller than a length of the slider plate.